Mixing and microfluidic apparatuses related thereto

ABSTRACT

The application relates to microfluidic apparatus and methods of use thereof. Provided in one example is a microfluidic device comprising: a first fluidic input and a second fluidic input; and a fluidic intersection channel to receive fluid from the first fluidic input and the second fluidic input, wherein the fluidic intersection channel opens into a first mixing chamber on an upper region of a first side of the first mixing chamber, wherein the first mixing chamber has a length, a width, and a depth, wherein the depth is greater than about 1.5 times a depth of the fluidic intersection channel; an outlet channel on an upper region of a second side of the first mixing chamber, wherein the outlet channel has a depth that is less than the depth of the first mixing chamber, and wherein an opening of the outlet channel is offset along a width of the second side of the first mixing chamber relative to the fluidic intersection.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of International patent applicationno. PCT/US2020/066541, filed Dec. 22, 2020, titled “MICROFLUIDICAPPARATUS AND METHODS OF USE THEREOF,” and which claims priority to U.S.provisional patent application No. 62/953,102, filed, Dec. 23, 2019, andtitled “MICROFLUIDIC APPARATUS AND METHODS OF USE THEREOF,” which isherein incorporated by reference in its entirety.

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specificationare herein incorporated by reference in their entirety to the sameextent as if each individual publication or patent application wasspecifically and individually indicated to be incorporated by reference.

BACKGROUND

Currently available technologies for manufacturing and formulatingpolynucleotide therapeutics, particularly mRNA therapeutics, oftenexpose the products to contamination and degradation. Currentlyavailable centralized production can be too costly, too slow, andsusceptible to contamination for use in therapeutic formulationspossibly including multiple polynucleotide species. Development ofscalable polynucleotide manufacturing, production of single patientdosages, elimination of touchpoints to limit contamination, input andprocess tracking for meeting clinical manufacturing requirements, anduse in Point-of-Care operations can advance the use of these promisingtherapeutic modalities. Microfluidic instrumentation and processes canprovide major advantages against these goals.

SUMMARY OF THE DISCLOSURE

The apparatuses and methods described herein may be used for themanufacture and formulation of biomolecule-containing products,particularly therapeutics for individualized care. In particular,described herein are closed path methods and apparatuses for processingtherapeutic polynucleotides at a point of care.

In general, described herein are apparatuses and method for formulatingcomposition using microfluidic devices. In particular, described hereinare methods and apparatuses that include formulating compositions usinga microfluidic mixing chamber (or a series of interconnectedmicrofluidic mixing chambers) that are configured to provide highlyefficient mixing in a relatively small footprint. These mixing chambersmay operate within a particular flow rate to achieve a high degree ofmixing. In some examples the mixing chambers may be cooled to atemperature that is below room temperature that enhancing mixing withinthe microfluidic mixing chambers described herein.

For example, the mixing chambers described herein may be referred to asbox mixing chambers and/or vortex mixing chambers. These mixing chambersmay be part of a microfluidic apparatus, e.g., microfluidic device,which may alternatively be referred to herein as a microfluidic pathdevice. These chambers may generally include a base, having a base(e.g., bottom) surface, and side walls, and a cover (e.g., top) surface,enclosing the chamber. These mixing chambers may also include an inlet,e.g., mixing inlet, that receives input from two or more fluid pathswithin (or into) the microfluidic device. The inlet feeds into a chamber(e.g., in some examples, a box-shaped chamber) near a region of one sideof the box chamber that is offset from the top and/or bottom, generallynear the upper region of the first side of the chamber. The inlet isgenerally offset from the top and/or bottom of the chamber by a depththat is greater than about 1.5 times the depth of the inlet. The inletmay also be referred to as the fluidic intersection channel. Forexample, the mixing inlet channel may include an opening into the mixingchamber at a first side wall of the vortex mixing chamber. Thesechambers may also include a mixing outlet channel. The mixing outletchannel may include an opening into the mixing chamber in a second sidewall of the vortex mixing chamber. In general, a vertical dimension ofthe vortex mixing chamber may be larger than a vertical dimension of themixing inlet channel and may be larger than a vertical dimension of themixing outlet channel.

The mixing channels described herein may receive two or more fluids fromthe inlet (e.g., a first fluid containing a first composition, such asan mRNA, and a second fluid containing a second composition, such as adelivery vehicle). The fluids (which may be combined prior to beingdriven into the mixing chamber), may extend into the mixing chamber andbe directed slightly downward and against the wall opposite from theinlet. This may form a curving or curling fluid path in which the fluidis directed across, down and under the inlet, to mix and combine backwith new material entering into the chamber from the inlet. The fluidmay continue to mix, eventually driving the mixed fluid out of theoutlet. In some examples the first mixing chamber is coupled to one ormore mixing chambers in series so that the adjacent mixing chambers feedinto each other in series. For example, the outlet of one chamber may befed into the inlet in another chamber. As will be described below, anyof these methods and apparatuses may include controlling the temperatureof the mixing chamber to a temperature or range of temperatures (in someexamples between about 10 and about 20 degrees C.) that is calibrated toenhance mixing for mixing in the mixing chambers described herein. Theenhanced mixing temperature may be based on the formulation being mixed(in some examples the sequence of the mRNA and/or the delivery vehicle)within the particular geometry of the mixing chamber. This optimaltemperature may be determined experimentally and/or by simulation. Asused herein, “delivery vehicle” refers to any substance thatfacilitates, at least in part, the in vivo, in vitro, or ex vivodelivery of a polynucleotide to targeted cells or tissues (e.g., tumors,etc.). Referring to something as a delivery vehicle need not necessarilymean that it may not also have therapeutic effects. In one example, thedelivery vehicle provides additional therapeutic effects. In anotherexample, the delivery vehicle does not provide additional therapeuticeffects. For example, a delivery vehicle may be an amino-lipidatedpeptoid delivery vehicle that may at least partially encapsulate anmRNA.

The apparatuses and methods described herein may be used with anyappropriate microfluidic apparatus (e.g., microfluidic device,microfluidic system, etc.), particularly those in which a high degree ofmixing is desired as part of an in-line, and in some examples, enclosed(e.g., closed-path) microfluidic path in which space may be a premium.Examples of microfluidic systems that may be used with any of the mixersand mixing techniques described herein may be found, for example, inSer. No. 16/989,833, titled “METHODS AND APPARATUSES FOR MANUFACTURINGFOR REMOVING MATERIAL FROM A THERAPEUTIC COMPOSITION,” and filed on Aug.10, 2020, which claims priority to U.S. provisional patent ApplicationNo. 62/885,159, entitled “MICROFLUIDIC APPARATUS AND METHODS OF USETHEREOF”, filed on Aug. 9, 2019, and to U.S. provisional patentapplication No. 62/885,170, entitled “METHODS AND APPARATUSES FORMANUFACTURING THERAPEUTIC COMPOSITIONS”, filed on Aug. 9, 2019, each ofwhich disclosures is herein incorporated by reference in its entirety.

Also described herein are microfluidic devices that include one or moremixers as described. For example, a microfluidic device may include: afirst fluidic input and a second fluidic input; and a fluidicintersection channel configured to receive fluid from the first fluidicinput and the second fluidic input, wherein the fluidic intersectionchannel opens into a first mixing chamber on an upper region of a firstside of the first mixing chamber, wherein the first mixing chamber has adepth that is greater than about 1.5 times a depth of the fluidicintersection channel; an outlet channel on an upper region of a secondside of the first mixing chamber, wherein the outlet channel has a depththat is less than the depth of the first mixing chamber, further whereinan opening of the outlet channel is offset along a width of the secondside of the first mixing chamber relative to the fluidic intersection.

A microfluidic device may include: a first fluidic input channel and asecond fluidic input channel, wherein the first and second fluidic inputchannels converge to form a fluidic intersection channel having a depthextending from a top surface to a first bottom surface and a width; afirst mixing chamber having a depth extending from the top surface to asecond bottom surface, a width extending from a first side to a secondside, and a length, wherein the depth of the first mixing chamber isgreater than the depth of the fluidic intersection channel and the widthof the first mixing chamber is greater than the width of the fluidicintersection channel, further wherein the first mixing chamber isfluidly connected to the fluidic intersection channel at the top surfaceand proximate the first side; and an outlet channel, wherein the outletchannel is fluidly connected to the first mixing chamber at the topsurface and proximate the second side of the mixing chamber.

A microfluidic device may include a first fluidic input and a secondfluidic input; and a fluidic intersection channel configured to receivefluid from the first fluidic input and the second fluidic input, whereinthe fluidic intersection channel opens into a first mixing chamber on anupper region of a first side of the first mixing chamber, wherein thefirst mixing chamber has a depth that is greater than about 1.5 times adepth of the fluidic intersection channel; a connection channel on anupper region of a second side of the first mixing chamber, wherein theconnection channel has a depth that is less than the depth of the firstmixing chamber, further wherein an opening of the connection channel isoffset along a width of the second side of the first mixing chamberrelative to the fluidic intersection, wherein the connection channelopens into a second mixing chamber; and an outlet channel extending fromthe second mixing chamber.

Any of these microfluidic devices may be configured as a single mixer inwhich the outlet channel forms a mixer output (e.g., without connectingin series to an additional mixing chamber). The outlet channel mayconnect to an output for the microfluidic device, or it may provide aninput for further processing, including for combining with another fluid(and subsequent mixing), etc. When the mixing chamber is configured as asingle mixer, the outlet channel does not act as the sole input to asecond mixing chamber connected in series with the first mixing chamber.

Any of these microfluidic devices may have a depth of the first mixingchamber that is between about 2 times and about 4 times the fluidicintersection channel depth. The depth of the first mixing chamber may beapproximately 3 times the fluidic intersection channel depth. In someexamples the width of the first mixing chamber is between about 1.5times and about 3 times the box length. For example, the width of thefirst mixing chamber may be approximately 2 times the box length.

The length of the first mixing chamber may be between about 2 times andabout 4 times the fluidic intersection channel length. In some examplesthe length of the first mixing chamber is approximately 3 times the boxlength.

In general, the mixers described herein may be integrated into amicrofluidics path device. For example, the fluidic intersectionchannel, first mixing chamber and outlet channel may all be formedwithin a first layer, further wherein the top surface of the fluidicintersection channel, first mixing chamber and outlet channel is formedof a second layer.

In general, the inlet and outlet into/out of the mixing chambersdescribed herein may be separated from each other by an offset. Forexample, the outlet channel may fluidly communicate with the firstmixing chamber at a first length of the mixing chamber and the fluidicintersection channel may fluidly communicate with the mixing chamber ata second length of the mixing chamber.

The mixing chamber may be a box having squared and/or rounded corners.For example, the first mixing chamber may have a corner radius ofbetween about 65-85 μm at all or some of the corners. As used hereinrounded refers to surfaces that transition smoothly, in a curve, ratherthan abruptly in an angle. A rounded corner may have a non-zero radiusof curvature that is, e.g., 0.5 times and 0.01 times the length of theshortest sidewall to which it connects.

The microfluidic device of any of the examples described herein may beconfigured to provide a change in fluid pressure through the firstmixing chamber at a flow rate of between about 0.25 ml/min and about 5ml/min (e.g., between about 0.25 ml/min and about 4 ml/min, betweenabout 0.25 ml/min and about 3 ml/min, between about 0.25 ml/min andabout 2 ml/min, between about 0.25 ml/min and about 1.5 ml/min, etc.)and between about 1 psi (6.9 kPa) and about 30 psi (206.8 kPa), e.g.,between about 1 psi and about 25 psi (about 6.9 kPa and about 172.4kPa), between about 1 psi and about 22.5 psi (about 6.9 kPa and 155.1kPa), between about 1 psi and about 20 psi (about 6.9 kPa and 137.9kPa), between 1 and 10 psi (about 6.9 kPa and 68.9 kPa), between 1 and 5psi (about 6.9 kPa and 34.5 kPa), etc.

A microfluidic device may include any number of mixing chambers that maybe connected in series. Thus, a microfluidic apparatus may include aplurality of fluidly connected mixing chambers. For example amicrofluidics path device may have a second mixing chamber having adepth extending from the top surface to a bottom surface of the secondmixing chamber, a width extending from a first side to a second side ofthe second mixing chamber, and a length, wherein the depth of the secondmixing chamber is greater than the depth of the outlet channel and thewidth of the second mixing chamber is greater than a width of the outletchannel, further wherein the second mixing chamber is fluidly connectedto the outlet channel at the top surface and proximate the second side;and a second outlet channel having a depth and a width, wherein thesecond outlet channel is fluidly connected to the second mixing chamberat the top surface and proximate the first side of the second mixingchamber.

Any of these microfluidic devices may include one or more fluid pumpsconfigured to pump fluid from the fluidic intersection channel into thefirst mixing chamber by deflecting at least a portion of an elasticmembrane within the microfluidic device. For example, the microfluidicdevice may include one or more fluid pumps between the plurality ofblending chambers and the microfluidic mixer, wherein the fluid pumpsare configured to pump fluid from the fluidic intersection channel intothe first mixing chamber by deflecting at least a portion of an elasticmembrane within the microfluidic device. Alternatively or additionally,any of these apparatuses (e.g., any of these microfluidic devices)described herein may use a non-pulsatile pressure source to drive fluidfrom the fluidic intersection channel into one or more mixing chambers.Thus, the flow through the mixer may be continuous and non-pulsing.

For example, any of these microfluidic devices may include a pluralityof pressure ports configured to deflect an elastic layer in themicrofluidic device to drive fluid between through the first mixingchamber.

In some examples the microfluidic device includes a flow restrictor influid communication with the first fluidic input, wherein the flowrestrictor comprises a serpentine elongate fluidic channel. In someexamples the outlet channel is in fluid communication with one or morefinal blending chambers.

In general, a microfluidic mixer (e.g., a mixing apparatus, mixingsystem, mixing device, microfluidics vortex mixing apparatus, etc.) mayinclude: a vortex mixing chamber comprising a base defining a bottomsurface, side walls, and an upper surface enclosing the vortex mixingchamber; a mixing inlet channel comprising an opening into the vortexmixing chamber at a first side wall of the vortex mixing chamber, amixing outlet channel comprising an opening into the vortex mixingchamber at a second side wall of the vortex mixing chamber, wherein avertical dimension of the vortex mixing chamber is larger than avertical dimension of the mixing inlet channel and is larger than avertical dimension of the mixing outlet channel.

The first side wall and the second side wall may be on opposing sidewalls of the vortex mixing chamber. In some examples the mixing inletchannel and the mixing outlet channel connect to the vortex mixingchamber at offset locations along the first side wall and the secondside wall. The height of the opening of the mixing inlet channel and theheight of the opening of the mixing outlet channel may be the same. Thewidth of the opening of the mixing inlet channel and the width of theopening of the mixing outlet channel may be the same.

The opening of the mixing inlet channel and the opening of the mixingoutlet channel may be disposed at a height of the respective first sidewall and second wall adjacent to the upper surface of the vortex mixingchamber.

The mixing inlet channel may have a first terminus comprising a fluidicintersection and a second terminus comprising the opening into thevortex mixing chamber. In some examples the fluidic intersection mayfurther comprise a first fluidic input channel and a second fluidicinput channel configured to intersect the mixing inlet channel at thefluidic intersection.

The first fluidic channel and the second fluidic channel may beconfigured to intersect at the fluidic intersection at an angle smallerthan 180 degrees with respect to each other. The first fluidic channeland the second fluidic channel may be configured to intersect at thefluidic intersection at an angle greater than 30 degrees with respect toeach other.

In some examples, the vortex mixing chamber, mixing inlet channel, andmixing outlet channel may be a first vortex mixing chamber, a firstmixing inlet channel, and a second mixing outlet channel, and themicrofluidic apparatus may further comprise a second microfluidic mixingapparatus comprising: a second vortex mixing chamber comprising a basedefining a bottom surface, side walls, and an upper surface enclosingthe second vortex mixing chamber; a second mixing inlet channelcomprising an opening into the second vortex mixing chamber at a firstside wall of the second vortex mixing chamber, a second mixing outletchannel comprising an opening into the second vortex mixing chamber at asecond side wall of the second vortex mixing chamber, wherein a verticaldimension of the second vortex mixing chamber is larger than a verticaldimension of the second mixing inlet channel and is larger than avertical dimension of the second mixing outlet channel.

As used herein a mixing apparatus may include a mixing system or amixing device. A mixing apparatus may equivalently be referred to hereinas a microfluidic mixer, or a microfluidic mixing device, or amicrofluidic mixing system.

Any of the microfluidic apparatuses described herein may include one ormore of: the first side wall and the second side wall of the secondvortex chamber are opposing side walls of the second vortex mixingchamber; the second mixing inlet channel and the second mixing outletchannel connect to the second vortex mixing chamber at offset locationsalong the first side wall and the second side wall of the second vortexchamber; a height of the opening of the second mixing inlet channel anda height of the opening of the second mixing outlet channel are thesame; a width of the opening of the second mixing inlet channel and awidth of the opening of the second mixing outlet channel are the same;the opening of the second mixing inlet channel and the opening of thesecond mixing outlet channel are disposed at a height of the respectivefirst side wall and second wall of the second vortex mixing chamberadjacent to the upper surface of the second vortex mixing chamber; andany combination thereof.

Any of the microfluidic apparatuses described herein may include asecond mixing outlet channel that comprises a first terminus at theopening into the second vortex mixing chamber.

The microfluidic mixers described herein may be included as part of amicrofluidic device (e.g., microfluidics chip) that is formed betweentwo layers, and may include one or more pumps, blending chambers, etc.For example, a microfluidic apparatus may include: a first plate and asecond plate; an elastic layer disposed between the first plate and thesecond plate; and a microfluidic path formed between the first plate andthe second plate, wherein the microfluidic flow path comprises: aplurality of blending chambers each comprising a fixed volume configuredto drive fluid between the blending chambers by deflecting at least aregion of the elastic layer; a microfluidic mixer, wherein themicrofluidic mixer comprises: a first fluidic input and a second fluidicinput; and a fluidic intersection configured to receive fluid from thefirst fluidic input and the second fluidic input, wherein the fluidicintersection opens into a first mixing chamber on an upper region of afirst side of the first mixing chamber, wherein the first mixing chamberhas a depth that is greater than about 1.5 times a depth of the fluidicintersection; a connection channel on an upper region of a second sideof the first mixing chamber, wherein the connection channel has a depththat is less than the depth of the first mixing chamber, further whereinan opening of the connection channel is offset along a width of thesecond side of the first mixing chamber relative to the fluidicintersection, wherein the connection channel opens into a second mixingchamber on an upper region of a first side of the second mixing chamber,further wherein the second mixing chamber has a depth that is greaterthan about 1.5 times a depth of the connection channel; and an outputchannel from the second mixing chamber on an upper region of a secondside of the second mixing chamber wherein the second side of the secondmixing chamber is opposite from the first side of the second mixingchamber.

An upper surface of the fluidic intersection may be configured to belevel with an upper surface of the first mixing chamber. In someexamples, an upper surface of the connection channel may be configuredto be level with an upper surface of the first mixing chamber and anupper surface of the second mixing chamber. In some examples, themicrofluidic apparatus may also include one or more fluid pumpsconfigured to pump fluid from the blending chamber into the microfluidicmixer by deflecting at least a portion of the elastic layer.

Any of these microfluidic apparatuses may include one or more fluidpumps between the plurality of blending chambers and the microfluidicmixer, wherein the fluid pumps are configured to pump fluid from theblending chamber into the microfluidic mixer by deflecting at least aportion of the elastic layer. For example, a microfluidic apparatus mayinclude a plurality of microfluidic mixers. In some examples theapparatus may include a plurality of pressure ports into the first plateconfigured to deflect the elastic layer to drive fluid between theblending chambers and through the microfluidic mixer.

In some examples the microfluidic apparatus includes a flow restrictorin fluid communication with the first fluidic input, wherein the flowrestrictor comprises a serpentine elongate fluidic channel. The outputchannel may be in fluid communication with one or more blendingchambers. The blending chamber may be a final blending chamber and/ormay include a pair of blending chambers having a fixed volume, eachblending chamber formed between the first plate and the second plate,wherein a portion of the elastic layer divides each chamber into afluid-contacting side in the second plate and a pressure-receiving sidein the first plate.

Any of the methods and apparatuses described herein including mixingusing one or more of the mixing chambers described herein may includemixing at a lower temperature (e.g., a mixing temperature) that isgenerally between about 1 and about 30 degrees C. (e.g., about 2 andabout 20 degrees C., e.g., between about 5 and about 18 degrees C.,between about 5 degrees C. and about 15 degrees C., etc.). The enhancedmixing temperature for a particular composition (e.g., therapeutic mRNAand/or delivery vehicle) and/or for the geometry of the mixing chamberand/or for the flow rate (fluid pressure, etc.) of the fluids beingmixed.

For example, a method of formulating a therapeutic mRNA with a deliveryvehicle may include mixing the mRNA and delivery vehicle in amicrofluidic mixing chamber at a temperature that is between about 2 andabout 20 degrees C., wherein the temperature is selected based on thecomposition of the mRNA and/or the composition of the delivery vehicle.The temperature may be selected based on one or more of: apolynucleotide sequence of the therapeutic mRNA; a sequence of thedelivery vehicle; a molecular weight of the delivery vehicle, amolecular weight of the therapeutic mRNA, a charge of the deliveryvehicle, a charge of the mRNA, a molecular weight of the deliveryvehicle; a molecular weight of the mRNA, a flow rate of the mRNA and/orthe delivery vehicle within the microfluidic mixing chamber, and adimension of the microfluidic mixing chamber.

In any of these methods and apparatuses, mixing may comprise mixing in amicrofluidic device comprising the microfluidic mixing chamber. Any ofthese methods may include separately maintaining the temperature of themixing chamber(s) relative to the rest of the microfluidic device.Mixing in the microfluidic mixing chamber may comprise passing the mRNAand delivery vehicle through a first opening into the mixing chamber ofa microfluidic device so that the mRNA and delivery vehicle are drivenagainst a wall of the mixing chamber and driven out of a plane of thefirst opening to a depth of greater than one times the depth of thefirst opening to form a mixed fluid comprising a therapeuticcomposition.

Passing may include driving the mRNA and delivery vehicle against thewall of the mixing chamber and out of a plane transverse to the firstopening to the depth of greater than about 2.5 times the depth of thefirst opening. The mRNA and delivery vehicle may be driven against thewall of the mixing chamber and out of a plane transverse to the firstopening to a depth of about 3 or more times the depth of the firstopening. The top of the first opening may be in line with the top of themixing chamber.

Also described are therapeutic compositions made using any of the methoddescribed herein. For example, described herein are therapeuticcompositions of mRNA and delivery vehicles made by mixing the mRNA anddelivery vehicle in a microfluidic mixing chamber at a temperature thatis between about 2 and about 20 degrees C., wherein the temperature isselected based on the composition of the mRNA and/or the composition ofthe delivery vehicle.

A method of mixing within a microfluidic device as described herein mayinclude: passing a first fluid and a second fluid through a firstopening into a mixing chamber within a microfluidic device, so that thefirst and second fluids are driven against a wall of the mixing chamberand driven out of a plane of the first opening to a depth of greaterthan one times the depth of the first opening to form a mixed fluid; andpassing the mixed fluid out of an outlet opening out of the mixingchamber; wherein the mixing chamber is maintained at a temperature ofbetween about 2 and about 20 degrees C.

A method of mixing within a microfluidic device may include: passing afirst fluid and a second fluid through at least one opening into amixing chamber within a microfluidic device, so that the first andsecond fluids are driven against a wall of the mixing chamber and drivenout of a plane of at least first opening; and passing the mixed fluidout of an outlet opening out of the mixing chamber; wherein the mixingchamber is maintained at a temperature of between about 2 and about 20degrees C.

In some examples of the methods described herein the method is a methodof mixing an oligonucleotide and delivery vehicle within a microfluidicdevice to form an aggregated nanoparticle and may include: passing afirst fluid containing oligonucleotide molecules and a second fluidcontaining delivery vehicle chemistry through at least one opening intoa mixing chamber within a microfluidic device, so that the first andsecond fluids are driven against a wall of the mixing chamber and drivenout of a plane of an opening; and passing the mixed fluid out of anoutlet opening out of the mixing chamber; wherein the mixing chamber ismaintained at a temperature of between about 2 and about 20 degrees C.

A method of mixing within a microfluidic device may include: passing afirst fluid and a second fluid through a first opening into a mixingchamber within a microfluidic device, so that the first and secondfluids are driven against a wall of the mixing chamber and out of aplane transverse to the first opening to a depth of greater than about2.5 times the depth of the first opening to form a uniformly mixedfluid; and passing the uniformly (or nearly uniformly) mixed fluid outof an outlet opening out of the mixing chamber, wherein the outletopening is opposite from the first opening but is offset from the firstopening; wherein the mixing chamber is maintained at a temperature ofbetween about 5 and about 20 degrees C. to uniformly mix the first andsecond fluid.

Passing the first fluid and the second fluid through the first openinginto the mixing chamber may include passing the first and second fluidsso that the first and second fluids are driven against the wall of themixing chamber and out of the plane transverse to the first opening tothe depth of greater than about 2.5 times the depth of the firstopening.

As mentioned above, in some examples the mixing chamber may bemaintained at a temperature of between about 5 and about 15 degrees C.to uniformly mix the first and second fluids; in some examples thetemperature of the mixture is maintained at between about 5 and about 15degrees C. (e.g., at approximately 10 degrees C.). Any of these methodsmay include passing the mixed fluid from the outlet opening into asecond opening into a second mixing chamber, so that the fluid is drivenagainst a wall of the second mixing chamber and driven out of a plane ofthe second opening to a depth of greater than one times the depth of thesecond opening to further mix the mixed fluid. For example, the fluidmay be driven against the wall of the mixing chamber and out of theplane transverse to the first opening to a depth of about 3 or moretimes the depth of the first opening. As mentioned, the top of the firstopening may be in line with the top of the first mixing chamber. In someexamples the outlet opening has a cross-section area that is equivalentto a cross-sectional area of the first opening. The mixing chamber maybe formed between a first layer and a second layer of the microfluidicspath device. The mixing chamber may have a length that is greater thanthe width, further wherein the length is greater than about 2 times thewidth of the first opening.

Also described herein are therapeutic compositions comprising an mRNAand a delivery vehicle (DV), made as described herein, e.g., by passinga first fluid comprising the mRNA and a second fluid comprising the DVthrough a first opening into a mixing chamber within a microfluidicdevice, so that the first and second fluids are driven against a wall ofthe mixing chamber and driven out of a plane of the first opening to adepth of greater than one times the depth of the first opening to form amixed fluid; and passing the mixed fluid out of an outlet opening out ofthe mixing chamber; wherein the mixing chamber is maintained at atemperature of between about 2 and about 20 degrees C.

Also described are methods of treatment using any of the compositionsformed as described herein. In some cases, these compositions may onlybe fabricated to the desired concentrations and volumes (and purity)when using the described methods. For example, a method of treating adisease may include: synthesizing one or more therapeutic mRNAs in amicrofluidic device, wherein the one or more therapeutic mRNAs arewithin a first fluid and a delivery vehicle for the one or moretherapeutic mRNAs is within a second fluid; passing the first fluid andthe second fluid through a first opening into a mixing chamber withinthe microfluidic device, so that the first and second fluids are drivenagainst a wall of the mixing chamber and driven out of a plane of thefirst opening to a depth of greater than one times the depth of thefirst opening to form a mixed fluid comprising a therapeuticcomposition; passing the mixed fluid out of an outlet opening out of themixing chamber, wherein the mixing chamber is maintained at atemperature of between about 2 and about 20 degrees C.; andadministering the therapeutic composition to a patient.

The mixing temperature, which may generally (but not necessarily) bebetween about 2 and about 20 degrees C., may be selected (as theenhanced mixing temperature) based on the dimensions of the mixer (e.g.,the box mixer), the composition of the mRNA (e.g., the therapeutic mRNA)and/or the composition of the delivery vehicle (DV). Thus any of themethods described herein may include calibrating or selecting thetemperature of the mixing chamber to set the enhanced mixingtemperature; the temperature of the mixing chamber(s) may be controlledseparately from the temperature(s) of other portions of the microfluidicdevice that includes the mixer. In some examples the mixing temperaturemay be calibrated or selected (to the enhanced mixing temperature) bymodeling the mixing in vitro or in vivo. For example, an optimal mixingtemperature may be estimated and/or set based on the mRNA composition(e.g., as a function of one or more of the percentages or ratios of thenucleotides making the mRNA(s), the length(s) of the mRNA(s), theconcentration of the mRNA(s), etc.). Additionally or alternatively, anoptimal mixing temperature may be estimated based on the composition ofthe delivery vehicle, such as but not limited to the molecular weight,the concentration, the charge, etc. For example, in some examplesselecting and/or setting the enhanced mixing temperature includesselecting a temperature between about 2 and about 20 degrees C. based onthe delivery vehicle and the one or more therapeutic mRNAs. In someexamples the optimal temperature may be greater than about 2-20 degrees(greater than about 2 degrees, greater than about 5 degrees, greaterthan about 10 degrees, greater than about 12.5 degrees, greater thanabout 15 degrees, greater than about 17.5 degrees, greater than about 20degrees, etc.). For example, in some examples the optimal temperaturerange may be between about 2 and about 50 degrees C. In some examplesthe optimal mixing temperate may be calculated or estimated in part onthe geometry of the mixing chamber(s) and/or the fluid pressure and/orflow rate of the material being mixed in the mixing chamber(s). Theoptimal mixing temperature may refer to the temperature that the mixingchamber may be held at during mixing in order to result in more uniformmixing following passage through the mixing chamber(s).

Passing the first fluid and the second fluid through the first openinginto the mixing chamber may include passing the first and second fluidsso that the first and second fluids are driven against the wall of themixing chamber and out of a plane transverse to the first opening to thedepth of greater than about 2.5 times the depth of the first opening.The fluid may be driven against the wall of the mixing chamber and outof a plane transverse to the first opening to a depth of about 3 or moretimes the depth of the first opening. In some examples, the top of thefirst opening is in line with the top of the mixing chamber. The outletopening may have a cross-section area that is equivalent to across-sectional area of the first opening. The mixing chamber may beformed between a first layer and a second layer of the microfluidicspath device. In some examples, the mixing chamber has a length that isgreater than the width, for example, the length may be greater thanabout 2 times the width of the first opening.

A method of forming a therapeutic composition to treat a disease mayinclude: passing one or more therapeutic mRNAs that are within a firstfluid and a delivery vehicle for the one or more therapeutic mRNAswithin a second fluid the second fluid through a first opening into amixing chamber within the microfluidic device, so that the first andsecond fluids are driven against a wall of the mixing chamber and drivenout of a plane of the first opening to a depth of greater than one timesthe depth of the first opening to form a mixed fluid comprising thetherapeutic composition; maintaining the temperature of the mixingchamber at a temperature determined by the one or more therapeuticand/or the delivery vehicle, wherein the temperature is between about 2and about 20 degrees C., while forming the mixed fluid; and passing themixed fluid out of an outlet opening out of the mixing chamber.

As mentioned above, any of these methods may include determining theoptimum mixing temperature. For example, maintaining the temperature ofthe mixing chamber may further include selecting and/or setting thetemperature of the mixing chamber to be the enhanced mixing temperature.The enhanced mixing temperature may be determined by may includemodeling the mixing in vitro and/or experimentally determining anenhanced mixing temperature in vivo. In any of these examples, selectingand/or setting of the enhanced mixing temperature may includedetermining the temperature or range of temperatures at which a yield ofmRNA (e.g., mRNA expression) in vivo or in vitro is maximized forvarious temperatures in order to enhance (e.g., increase) the productionof active compounds. Thus, the enhanced mixing temperature may includethe temperature or range of temperatures at which mixing occurs for mRNAexpression in the system(s) described herein. Determining and/or settingthe enhanced mixing temperature may include selecting a temperaturebetween about 2 and about 20 degrees C. based on the delivery vehicleand the one or more therapeutic mRNAs.

For example, described herein are microfluidic devices comprising: afirst fluidic input and a second fluidic input; and a fluidicintersection channel to receive fluid from the first fluidic input andthe second fluidic input, wherein the fluidic intersection channel opensinto a first mixing chamber on an upper region of a first side of thefirst mixing chamber, wherein the first mixing chamber has a length, awidth, and a depth, wherein the depth is greater than about 1.5 times adepth of the fluidic intersection channel; an outlet channel on an upperregion of a second side of the first mixing chamber, wherein the outletchannel has a depth that is less than the depth of the first mixingchamber, and wherein an opening of the outlet channel is offset along awidth of the second side of the first mixing chamber relative to thefluidic intersection.

A microfluidic device may include: a first fluidic input channel and asecond fluidic input channel, wherein the first and second fluidic inputchannels converge to a fluidic intersection channel having width and adepth extending from a top surface to a first bottom surface; a firstmixing chamber having a depth extending from the top surface to a secondbottom surface, a width extending from a first side to a second side,and a length, wherein the depth of the first mixing chamber is greaterthan the depth of the fluidic intersection channel and the width of thefirst mixing chamber is greater than the width of the fluidicintersection channel, and wherein the first mixing chamber is fluidlyconnected to the fluidic intersection channel at the top surface andproximate the first side; and an outlet channel, wherein the outletchannel is fluidly connected to the first mixing chamber at the topsurface and proximate the second side of the first mixing chamber.

A microfluidic device may include: a first fluidic input and a secondfluidic input; and a fluidic intersection channel to receive fluid fromthe first fluidic input and the second fluidic input, wherein thefluidic intersection channel opens into a first mixing chamber on anupper region of a first side of the first mixing chamber, wherein thefirst mixing chamber has a width, a length and a depth, wherein thedepth is greater than about 1.5 times a depth of the fluidicintersection channel; a connection channel on an upper region of asecond side of the first mixing chamber, wherein the connection channelhas a depth that is less than the depth of the first mixing chamber,further wherein an opening of the connection channel is offset along thewidth of the second side of the first mixing chamber relative to thefluidic intersection, wherein the connection channel opens into a secondmixing chamber; and an outlet channel extending from the second mixingchamber.

In any of these microfluidic devices the depth of the first mixingchamber may be between about 2 times and about 4 times the fluidicintersection channel depth. The depth of the first mixing chamber may beabout 3 times the fluidic intersection channel depth. The width of thefirst mixing chamber may be between about 1.5 times and about 3 timesthe box length. The width of the first mixing chamber may be about 2times the box length. The length of the first mixing chamber may bebetween about 2 times and about 4 times the fluidic intersection channellength. The length of the first mixing chamber may be about 3 times thebox length.

The fluidic intersection channel, first mixing chamber and outletchannel may all be within a first layer, and wherein the top surface ofthe fluidic intersection channel, first mixing chamber and outletchannel comprises a second layer. The outlet channel may fluidlycommunicate with the first mixing chamber at a first length of themixing chamber and the fluidic intersection channel fluidly communicateswith the mixing chamber at a second length of the mixing chamber.

The first mixing chamber may have rounded corners. The first mixingchamber may have a corner radius of between about 65 and about 85 μm.The change in fluid pressure through the first mixing chamber at a flowrate of between 0.25 and 5 ml/min may be between about 6.9 kPa and about206.8 kPa. The width of the first mixing chamber may be between about150 and about 600 μm, the depth of the first mixing chamber may bebetween about 150 and about 500 μm, and the length of the first mixingchamber may be between about 500 μm and about 1000 μm.

The connecting channel may have a width that is between about 75 μm andabout 225 μm, a depth that is between about 75 μm and about 225 μm, anda length that is between about 225 and about 550 μm.

Any of these microfluidic devices may include: a second mixing chamberhaving a depth extending from the top surface to a bottom surface of thesecond mixing chamber, a width extending from a first side to a secondside of the second mixing chamber, and a length, wherein the depth ofthe second mixing chamber is greater than the depth of the outletchannel and the width of the second mixing chamber is greater than awidth of the outlet channel, further wherein the second mixing chamberis fluidly connected to the outlet channel at the top surface andproximate the second side; and a second outlet channel having a depthand a width, wherein the second outlet channel is fluidly connected tothe second mixing chamber at the top surface and proximate the firstside of the second mixing chamber.

Any of the microfluidic devices described herein may have one or morefluid pumps to pump fluid from the fluidic intersection channel into thefirst mixing chamber by deflecting at least a portion of an elasticmembrane within the microfluidic device. Any of the microfluidic devicedescribed herein may have one or more fluid pumps between the pluralityof blending chambers and the microfluidic mixer, wherein the fluid pumpsare to pump fluid from the fluidic intersection channel into the firstmixing chamber by deflecting at least a portion of an elastic membranewithin the microfluidic device.

A microfluidic device may include a plurality of fluidly connectedmixing chambers including the first mixing chamber.

Any of the microfluidic devices described herein may include a pluralityof pressure ports configured to deflect an elastic layer in themicrofluidic device to drive fluid between through the first mixingchamber. Any of the microfluidic devices described herein may include aflow restrictor in fluid communication with the first fluidic input,wherein the flow restrictor comprises a serpentine elongate fluidicchannel.

A microfluidic mixing apparatus may include: a mixing chamber (e.g.,comprising a base defining a bottom surface, side walls, and an uppersurface enclosing the mixing chamber); a mixing inlet channel (e.g.,comprising an opening into the mixing chamber at a first side wall ofthe mixing chamber); a mixing outlet channel (e.g., comprising anopening into the mixing chamber at a second side wall of the mixingchamber), or any combination of these. A vertical dimension of themixing chamber may be larger than a vertical dimension of the mixinginlet channel and may be larger than a vertical dimension of the mixingoutlet channel.

The first side wall and the second side wall may be opposing side wallsof the mixing chamber. The mixing inlet channel and the mixing outletchannel may connect to the mixing chamber at offset locations along thefirst side wall and the second side wall. The height of the opening ofthe mixing inlet channel and the height of the opening of the mixingoutlet channel may be the same. The width of the opening of the mixinginlet channel and the width of the opening of the mixing outlet channelmay be the same.

The opening of the mixing inlet channel and the opening of the mixingoutlet channel may be disposed at a height of the respective first sidewall and second wall adjacent to the upper surface of the mixingchamber. The mixing inlet channel may have a first terminus comprising afluidic intersection and a second terminus comprising the opening intothe mixing chamber.

The fluidic intersection may further comprise a first fluidic inputchannel and a second fluidic input channel that intersect the mixinginlet channel at the fluidic intersection. The first fluidic channel andthe second fluidic channel may intersect at the fluidic intersection atan angle smaller than about 180 degrees with respect to each other. Thefirst fluidic channel and the second fluidic channel may intersect atthe fluidic intersection at an angle greater than about 30 degrees withrespect to each other.

The mixing chamber may be a first mixing chamber, the mixing inletchannel may be a first mixing inlet channel, and/or the mixing outletchannel may be a first mixing outlet channel. The microfluidic apparatusmay further comprise a second microfluidic mixing apparatus comprising:a second mixing chamber comprising a base defining a bottom surface,side walls, and an upper surface enclosing the second mixing chamber; asecond mixing inlet channel comprising an opening into the second mixingchamber at a first side wall of the second mixing chamber, a secondmixing outlet channel comprising an opening into the second mixingchamber at a second side wall of the second mixing chamber, wherein avertical dimension of the second mixing chamber is larger than avertical dimension of the second mixing inlet channel and is larger thana vertical dimension of the second mixing outlet channel.

The first side wall and the second side wall of the second chamber maybe opposing side walls of the second mixing chamber; the second mixinginlet channel and the second mixing outlet channel may connect to thesecond mixing chamber at offset locations along the first side wall andthe second side wall of the second chamber; a height of the opening ofthe second mixing inlet channel and a height of the opening of thesecond mixing outlet channel may be the same; and a width of the openingof the second mixing inlet channel and a width of the opening of thesecond mixing outlet channel may be the same.

The microfluidic apparatus of any one of claims 23-34, wherein thesecond mixing outlet channel comprises a first terminus at the openinginto the second mixing chamber.

Also described herein are microfluidic apparatuses comprising cascadingmicrofluidic mixing apparatuses, wherein each of the cascadingmicrofluidic mixing apparatuses may include: a mixing chamber (e.g.,comprising a base defining a bottom surface, side walls, and an uppersurface); a mixing inlet channel (e.g., comprising an opening into themixing chamber at a first side wall of the mixing chamber); a mixingoutlet channel (e.g., comprising an opening into the mixing chamber at asecond side wall of the mixing chamber), or any combination of these. Avertical dimension of the mixing chamber may be larger than a verticaldimension of the mixing inlet channel and may be larger than a verticaldimension of the mixing outlet channel. Further, cascading microfluidicmixers may be connected to one another in a series so that the mixinginlet channel of each of the cascading microfluidic mixers after a firstmicrofluidic mixer in the series may be connected to the mixing outletof a prior microfluidic mixer in the series.

A microfluidic apparatus may comprise: a first plate and a second plate;an elastic layer disposed between the first plate and the second plate;and a microfluidic path between the first plate and the second plate,wherein the microfluidic path comprises: a plurality of blendingchambers each comprising a fixed volume separated by a portion of theelastic layer, wherein the portion of the elastic layer is configured todeflect to drive fluid between blending chambers of the plurality ofblending chambers; a first microfluidic mixer, wherein the firstmicrofluidic mixer comprises: a first fluidic input and a second fluidicinput; a fluidic intersection to receive fluid from the first fluidicinput and the second fluidic input, wherein the fluidic intersectionopens into a first mixing chamber on an upper region of a first side ofthe first mixing chamber, wherein the first mixing chamber has a depththat is greater than 1.5 times a depth of the fluidic intersection; aconnection channel on an upper region of a second side of the firstmixing chamber, wherein the connection channel has a depth that is lessthan the depth of the first mixing chamber, further wherein an openingof the connection channel is offset along a width of the second side ofthe first mixing chamber relative to the fluidic intersection, whereinthe connection channel opens into a second mixing chamber on an upperregion of a first side of the second mixing chamber, further wherein thesecond mixing chamber has a depth that is greater than 1.5 times a depthof the connection channel; and an output channel from the second mixingchamber on an upper region of a second side of the second mixing chamberwherein the second side of the second mixing chamber is opposite fromthe first side of the second mixing chamber.

An upper surface of the fluidic intersection may be substantially levelwith an upper surface of the first mixing chamber. An upper surface ofthe connection channel may be configured to be level with an uppersurface of the first mixing chamber and an upper surface of the secondmixing chamber.

Any of the microfluidic apparatuses described herein may include one ormore fluid pumps to pump fluid from the blending chamber into the firstmicrofluidic mixer by deflecting at least a portion of the elasticlayer. The microfluidic apparatuses described herein may include one ormore fluid pumps between the plurality of blending chambers and thefirst microfluidic mixer, wherein the fluid pumps are to pump fluid fromthe blending chamber into the first microfluidic mixer by deflecting atleast a portion of the elastic layer.

The microfluidic apparatus may comprise a plurality of microfluidicmixers including the first microfluidic mixer, and/or a plurality ofpressure ports into the first plate configured to deflect the elasticlayer to drive fluid between the blending chambers and through the firstmicrofluidic mixer. Any of the microfluidic apparatuses described hereinmay include a flow restrictor in fluid communication with the firstfluidic input, wherein the flow restrictor comprises a serpentineelongate fluidic channel.

The final blending chamber may comprise a pair of blending chambershaving a fixed volume, each blending chamber is disposed between thefirst plate and the second plate, and wherein a portion of the elasticlayer divides each chamber into a fluid-contacting side in the secondplate and a pressure-receiving side in the first plate.

Also described herein are methods of formulating a therapeutic mRNA witha delivery vehicle, the method comprising mixing the mRNA and thedelivery vehicle in a microfluidic mixing chamber at a temperature thatis between about 2 and about 20 degrees C., wherein the temperature isselected using at least the composition of the mRNA, the composition ofthe delivery vehicle, or a combination thereof.

Any of these methods may include selecting the temperature using atleast: a polynucleotide sequence of the therapeutic mRNA; a sequence ofthe delivery vehicle; a molecular weight of the delivery vehicle, amolecular weight of the therapeutic mRNA, a charge of the deliveryvehicle, a charge of the mRNA, a molecular weight of the deliveryvehicle; a molecular weight of the mRNA, a flow rate of the mRNA and/orthe delivery vehicle within the microfluidic mixing chamber, and adimension of the microfluidic mixing chamber, or any combinationthereof.

Mixing may include mixing in a microfluidic device comprising themicrofluidic mixing chamber.

Any of these methods may include separately maintaining the temperatureof the mixing chamber to be between about 2 and about 20 degrees C.,relative to the rest of the microfluidic device. Mixing in themicrofluidic mixing chamber may include passing the mRNA and thedelivery vehicle through a first opening into the mixing chamber of amicrofluidic device so that the mRNA and the delivery vehicle are drivenagainst a wall of the mixing chamber and driven out of a plane of thefirst opening to a depth of greater than one times the depth of thefirst opening. The methods described herein may include passing thatcomprises driving the mRNA and the delivery vehicle against the wall ofthe mixing chamber and out of a plane transverse to the first opening tothe depth of greater than about 2.5 times the depth of the firstopening.

The mRNA and the delivery vehicle may be driven against the wall of themixing chamber and out of a plane transverse to the first opening to adepth of 3 or more times the depth of the first opening. A top of thefirst opening may be in line with a top of the mixing chamber.

Also described herein are methods of mixing including: passing a firstfluid and a second fluid through a first opening into a mixing chamberin a microfluidic device, so that the first and second fluids are drivenagainst a wall of the mixing chamber and driven out of a plane of thefirst opening to a depth of greater than one times the depth of thefirst opening to form a mixed fluid; and passing the mixed fluid out ofan outlet opening out of the mixing chamber; wherein the mixing chamberis maintained at a temperature of between about 2 and about 20 degreesC.

A method of mixing may include: passing a first fluid and a second fluidthrough at least one opening into a mixing chamber within a microfluidicdevice, so that the first and second fluids are driven against a wall ofthe mixing chamber and driven out of a plane of at least first opening;and passing the mixed fluid out of an outlet opening out of the mixingchamber; wherein the mixing chamber is maintained at a temperature ofbetween 2 and 20 degrees C.

Also described herein are methods of mixing, the method comprising:passing a first fluid containing oligonucleotide molecules and a secondfluid containing delivery vehicle chemistry through at least one openinginto a mixing chamber in a microfluidic device, so that the first andsecond fluids are driven against a wall of the mixing chamber and drivenout of a plane of an opening; and passing the mixed fluid out of anoutlet opening out of the mixing chamber; wherein the mixing chamber ismaintained at a temperature of between about 2 and about 20 degrees C.

A method of mixing within a microfluidic device may include: passing afirst fluid and a second fluid through a first opening into a mixingchamber within a microfluidic device, so that the first and secondfluids are driven against a wall of the mixing chamber and out of aplane transverse to the first opening to a depth of greater than about2.5 times the depth of the first opening to form a substantially mixedfluid; and passing the mixed fluid out of an outlet opening out of themixing chamber, wherein the outlet opening is opposite from the firstopening but is offset from the first opening; wherein the mixing chamberis maintained at a temperature of between about 5 and about 20 degreesC.

Passing the first fluid and the second fluid through the first openinginto the mixing chamber may comprise passing the first and second fluidsso that the first and second fluids are driven against the wall of themixing chamber and out of the plane transverse to the first opening tothe depth of greater than about 2.5 times the depth of the firstopening.

Any of the methods described herein may include maintaining thetemperature of the mixing chamber between about 5 and about 15 degreesC. The methods described herein may include maintain the temperature ofthe mixed fluid at between about 5 and about 15 degrees C. The methoddescribed herein may include maintaining a temperature of the mixedfluid at about 10 degrees C. The methods described herein may includepassing the mixed fluid from the outlet opening into a second openinginto a second mixing chamber, so that the fluid is driven against a wallof the second mixing chamber and driven out of a plane of the secondopening to a depth of greater than one times the depth of the secondopening to further mix the mixed fluid. The fluid may be driven againstthe wall of the mixing chamber and out of the plane transverse to thefirst opening to a depth of about 3 or more times the depth of the firstopening.

In any of these methods, a top of the first opening may be in line witha top of the first mixing chamber. The outlet opening may have across-section area that is equal to a cross-sectional area of the firstopening. The mixing chamber may be between a first layer and a secondlayer of the microfluidic device. The mixing chamber may have a lengththat is greater than the width, and the length may be greater than about2 times the width of the first opening.

Also described herein are methods of forming a composition comprising:synthesizing one or more therapeutic mRNAs in a microfluidic device,wherein the one or more therapeutic mRNAs are within a first fluid and adelivery vehicle for the one or more therapeutic mRNAs is within asecond fluid; passing the first fluid and the second fluid through afirst opening into a mixing chamber in the microfluidic device, so thatthe first and second fluids are driven against a wall of the mixingchamber and driven out of a plane of the first opening to a depth ofgreater than one times the depth of the first opening to form a mixedfluid, wherein the mixing chamber is maintained at a temperature that isselected to enhance mixing of the therapeutic mRNA and delivery vehicle;and passing the mixed fluid out of an outlet opening out of the mixingchamber. The temperature may be selected to enhance (e.g., increase)mixing as compared to mixing with all other parameters (except thetemperature) are kept substantially constant; as described herein, thismay result in mixing at lower temperatures to the same level or better(e.g., temperatures between 2 degrees C. and 20 degrees C.).

For example, the mixing chamber may be maintained at the temperaturethat is selected to enhance mixing of for the therapeutic mRNA anddelivery vehicle and is between 2 and 20 degrees C.

Any of these methods may include selecting an enhanced mixingtemperature of the mixing chamber. Selecting the enhanced mixingtemperature may include modeling the mixing in vitro or in vivo.Selecting the enhanced mixing temperature may include selecting atemperature between about 2 and about 20 degrees C. based on thedelivery vehicle and the one or more therapeutic mRNAs. The passing thefirst fluid and the second fluid through the first opening into themixing chamber may include passing the first and second fluids so thatthe first and second fluids are driven against the wall of the mixingchamber and out of a plane transverse to the first opening to the depthof greater than about 2.5 times the depth of the first opening. Thefluid may be driven against the wall of the mixing chamber and out of aplane transverse to the first opening to a depth of about 3 or moretimes the depth of the first opening. The top of the first opening maybe in line with a top of the mixing chamber. The outlet opening may havea cross-section area that is equal to a cross-sectional area of thefirst opening. The mixing chamber may be between a first layer and asecond layer of the microfluidic device. The mixing chamber may have alength that is greater than a width, further the length may be greaterthan 2 times the width of the first opening.

Also described herein are methods of forming a therapeutic composition,the method comprising: passing one or more therapeutic mRNAs within afirst fluid and a delivery vehicle for the one or more therapeutic mRNAswithin a second fluid through a first opening into a mixing chamber in amicrofluidic device, so that the first and second fluids are drivenagainst a wall of the mixing chamber and driven out of a plane of thefirst opening to a depth of greater than one times the depth of thefirst opening to form a mixed fluid comprising the therapeuticcomposition; maintaining a temperature of the mixing chamber at anenhanced mixing temperature determined to enhance mixing; and passingthe mixed fluid out of an outlet opening out of the mixing chamber.

The enhanced mixing temperature may be between about 2 and about 20degrees C. Maintaining may include determining the enhanced mixingtemperature for the one or more therapeutic mRNAs and/or the deliveryvehicle.

Any of the methods described herein may include determining the enhancedmixing temperature by modeling the mixing in vitro or in vivo. Any ofthese methods may include determining the enhanced mixing temperature byselecting a temperature between about 2 and about 20 degrees C. havinggreater mixing as compared to mixing at other temperatures between about2 and about 20 degrees C. Thus, the enhanced mixing temperature may be atemperature within the range of about 2-20 degrees C. in which themixing is at or near a maximum as compared to other temperatures withinthis temperature range. The enhanced mixing temperature may not be thepeak (maximum) value, but may be within range of the temperaturecorresponding to the peak mixing value (e.g., within 2 degrees, within1.5 degrees, within 1 degree, within 0.5 degrees, within 0.2 degrees,within 0.2 degrees, etc.).

The passing the first fluid and the second fluid through the firstopening into the mixing chamber may comprise passing the first andsecond fluids so that the first and second fluids are driven against thewall of the mixing chamber and out of a plane transverse to the firstopening to the depth of greater than about 2.5 times the depth of thefirst opening. The fluid may be driven against the wall of the mixingchamber and out of a plane transverse to the first opening to a depth ofabout 3 or more times the depth of the first opening. A top of the firstopening may be in line with a top of the mixing chamber. The outletopening may have a cross-section area that is equivalent to across-sectional area of the first opening. The mixing chamber may beformed between a first layer and a second layer of the microfluidicdevice. The mixing chamber may have a length that is greater than thewidth, and the length may be greater than 2 times the width of the firstopening.

Also described herein are methods of mixing that include: passing afirst fluid and a second fluid through a first opening into a mixingchamber in a microfluidic device, so that the first and second fluidsare driven against a wall of the mixing chamber and driven out of aplane of the first opening to a depth of greater than one times thedepth of the first opening to form a mixed fluid; and passing the mixedfluid out of an outlet opening out of the mixing chamber.

The methods of mixing described herein may include passing the firstfluid and the second fluid through the first opening into the mixingchamber so that the first and second fluids are driven against the wallof the mixing chamber and out of the plane transverse to the firstopening to the depth of greater than about 2.5 times the depth of thefirst opening.

Any of the methods of mixing described herein may be single mixingchamber mixers in which only a single mixing chamber (e.g., box mixer)is used, which can achieve substantially complete mixing. Thus, thesesingle mixing chambers may achieve a high level of mixing in a verysmall footprint in a microfluidic device. The mixed fluid may besubstantially mixed by the mixing chamber and the mixing chamber may beconfigured as a single mixer that does not connect to a second mixingchamber.

For example, a method of mixing within a microfluidic device mayinclude: passing a first fluid and a second fluid through a firstopening into a mixing chamber within a microfluidic device, so that thefirst and second fluids are driven against a wall of the mixing chamberand out of a plane transverse to the first opening to a depth of greaterthan about 2.5 times the depth of the first opening to form asubstantially mixed fluid; and passing the mixed fluid out of an outletopening out of the mixing chamber, wherein the outlet opening isopposite from the first opening but is offset from the first opening,wherein the mixed fluid is substantially mixed by the mixing chamber andthe mixing chamber is configured as a single mixer that does not connectto a second mixing chamber.

Alternatively, these methods may be configured so that mixing isperformed by linking, in series, two or more (e.g., 3, 4, 5, 6, etc.)mixing chambers. For example, a method may include passing the mixedfluid from the outlet opening into a second opening into a second mixingchamber, so that the fluid is driven against a wall of the second mixingchamber and driven out of a plane of the second opening to a depth ofgreater than one times the depth of the second opening to further mixthe mixed fluid.

The fluid may be driven against the wall of the mixing chamber and outof the plane transverse to the first opening to a depth of about 3 ormore times the depth of the first opening. The outlet opening may have across-section area that is equal to a cross-sectional area of the firstopening. The mixing chamber may have a length that is greater than thewidth, and wherein the length is greater than about 2 times the width ofthe first opening. The mixing chamber may have rounded corners. Thechange in fluid pressure through the mixing chamber at a flow rate ofbetween 0.25 and 5 ml/min may be between about 6.9 kPa and about 206.8kPa. The width of the mixing chamber may be between about 150 and about600 μm, the depth of the mixing chamber may be between about 150 andabout 500 μm, and the length of the mixing chamber may be between about500 μm and about 1000 μm.

All of the methods and apparatuses described herein, in any combination,are herein contemplated and can be used to achieve the benefits asdescribed herein.

BRIEF DESCRIPTION OF THE DRAWINGS

The novel features of the invention are set forth with particularity inthe claims that follow. A better understanding of the features andadvantages of the present invention will be obtained by reference to thefollowing detailed description that sets forth illustrative examples, inwhich the principles of the invention are utilized, and the accompanyingdrawings of which:

FIGS. 1A and 1B are schematic representations of mixing apparatusaccording to some examples of the disclosure.

FIGS. 2A to 2C schematically illustrates mixing behavior for one exampleof a mixing apparatus.

FIGS. 2D and 2E illustrate another example of a mixing apparatus asdescribed herein, showing the mixing of ethanol:water.

FIGS. 2F and 2G illustrate another example of a mixing apparatus asdescribed herein, showing the mixing of ethanol:water.

FIGS. 2H and 2I illustrate another example of a mixing apparatus asdescribed herein, showing the mixing of ethanol:water.

FIG. 2J illustrates mixing in another example of a mixing apparatus asdescribed herein.

FIG. 3A schematically illustrates one example of an apparatus (e.g.,microfluidic apparatus) including a mixer (e.g., mixing apparatus) asdescribed herein.

FIGS. 3B and 3C illustrate an example of a microfluidic apparatusincluding a mixer as described herein. FIG. 3C shows an enlarged view ofthe mixer (mixing apparatus) of FIG. 3B.

FIG. 3D shows another example of a mixer of a microfluidic apparatushaving a short distance between the output of the mixer a junction witha dilution buffer. FIG. 3E is an example of an apparatus having a longerdistance between the output of the mixer and a junction with a dilutionbuffer.

FIG. 4 is a schematic representation of selected characteristics for anexample apparatus including an example mixer according to some examplesof the disclosure.

FIG. 5 is a schematic representation of an example apparatus includingan example mixer and processing components according to some examples ofthe disclosure.

FIG. 6 is a graph illustrating, in one example, the effect oftemperature (e.g., cooling) on mixing using a mixing apparatus asdescribed herein.

FIGS. 7A-7D illustrate examples of mixing apparatuses of differentconfigurations. FIG. 7A shows a one-chamber mixing apparatus. FIG. 7Bshows a three serially connected mixers as described herein. FIG. 7Cshows an example of six serially connected mixers as described herein.FIG. 7D shows an example of twelve serially connected mixers asdescribed herein.

FIG. 8 is a picture illustrating a mixing apparatus including threeserially connected mixers showing deposition within the mixers.

FIGS. 9A-9B show a first example of mixing apparatus having threeserially connected mixers (“3 box” mixers) of different sizes. In FIG.9A each mixer of the mixing apparatus forms a box of 250 μm by 200 μm by500 μm. In FIG. 9B, each mixer of the mixing apparatus is scaled up bytwofold compared to the apparatus shown in FIG. 9A, so that each boxforming each mixer is 500 μm by 400 μm by 1000 μm.

FIG. 9C is a graph comparing the mixing effects of the larger (scaledup) mixing apparatus shown in FIG. 9B (“3 box L”) and the mixingapparatus shown in FIG. 9A (“3 box”). The bar graph shows the Z-averagevalue, scale on left, while the dots show the polydispersity index(PDI), scale on the right.

FIG. 10A shows a mixing apparatus including three mixers connected inseries, as described herein. FIG. 10B shows a similar mixing apparatusto that shown in FIG. 10A, but with the corner regions rounded, whichmay reduce, and in some instances even eliminate, dead regions (regionsof little fluid flow) within the mixer.

FIGS. 11A and 11B illustrate an example of a mixing apparatus havingthree mixers connected in series at an angle that is greater than 90degrees, but less than 180 degrees. FIG. 11A shows a top perspectiveview of the mixing apparatus, while FIG. 11B shows a sectional viewthrough an upper (top) region of the mixing apparatus. The angle betweenadjacent mixers in FIGS. 11A and 11B is 135 degrees.

FIG. 11C is a graph illustrating the mixing effects of differentconfigurations of mixing apparatuses, including a mixing apparatushaving a 135 degree angle (“3 box angle,” as shown in FIGS. 11A-11B) anda curved mixing apparatus (“3 box curved,” as shown in FIGS. 10A-10B),compared to a mixing apparatus such as shown in FIG. 7B having threemixers connected in series (“3 box”), or a mixing apparatus such asshown in FIG. 7A having a single mixer (“1 box”). In FIG. 11C, the bargraph shows the Z-average value, scale on left, while the dots show thepolydispersity index (PDI), scale on the right.

FIG. 12A shows another example of a mixing apparatus including threemixers connected in series, as described herein. FIG. 12B shows anexample of an apparatus that does not include the step from a narrowerheight channel into the deeper box of the mixer.

FIG. 12C is a graph showing the particle size (due to mixing) followingmultiple runs through a mixing apparatus as shown in FIG. 12A (“3 box”)or through a linear mixing channel as shown in FIG. 12B (“3 boxplanar”), showing visibly smaller particle sizes (and therefore moreefficient mixing) in the mixing apparatus of FIG. 12A as compared toFIG. 12B.

FIG. 13 is a graph illustrating the effects of flow rate through amixing apparatus having three mixers (“3 box” mixer) similar to thatshown in FIGS. 7B, 9A, and 10A, showing that higher flow rates haveresulted in smaller particle sizes, and visibly better mixing ascompared with hand mixing. In FIG. 13, the bar graphs show the volumemean values, scale on left, while the dots show the polydispersity index(PDI), scale on the right. Four instances of 1 ml/min are shown, fourinstances at 2 ml/min are shown, and 2 instances of 4 ml/min are shown,along with a single hand mixed sample.

FIGS. 14A-14B illustrate one example of a dialyzer, shown in perspectiveand cross-sectional views, respectively.

FIG. 15 is a cross-sectional view of one example of an edge region of adialyzer similar to that shown in FIGS. 14A-14B.

FIG. 16 illustrates one example of a dialyzer as described herein,showing exemplary flow rate (velocity) through the device.

FIGS. 17A-17C are illustrations of flow rate through another example ofa dialyzer apparatus as shown herein, showing flow rate through thedevice.

FIG. 18 is an example of a concentrator as described herein.

FIG. 19 schematically illustrates an example of a microfluidics pathdevice as described herein, including both mixing (using one or morevortex mixing chambers), dialysis, and concentration.

FIG. 20 is a schematic representation of pressure characteristics of amicrofluidic apparatus including microfluidic mixers (e.g., box mixers),formulating components, and a concentrator according to some embodimentsof the disclosure.

DETAILED DESCRIPTION

In general, described herein are apparatuses (e.g., systems, devices,etc.) and methods for processing fluid mixtures, including but notlimited to therapeutic polynucleotides. In particular, described hereinare mixing apparatuses that may mix materials in a microfluidicapparatus more quickly and efficiently, using less microfluidic space,than previously described microfluidic mixers. Any of the mixingapparatuses described herein may include one or more mixers, which maybe referred to as box mixers or vortex mixers; which may be connected inseries and may be included as part of a microfluidic apparatus. Forexample, any of these apparatuses and methods may be used as part of aclosed path microfluidic apparatus and method that may be configured tominimize, and in some instances even eliminate, manual handling. Aclosed path apparatus and method may provide a substantially asepticenvironment and may form a sterile path for processing from initialinput (e.g., template) to output (compounded therapeutic). As usedherein, the term “substantially” may refer to mostly or essentiallyall/essentially completely (e.g., greater than 90%, greater than 95%,greater than 97.5%, greater than 99%, greater than 99.5%, greater than99.9%, etc.), and may include all or completely. For example,“substantially mixed” may refer to a mixture that is mostly orcompletely mixed, that is, mixed to homogeneity. Material inputs(nucleotides, and any chemical components) into the apparatus may besterile and may be input into the system without requiring virtually anymanual interaction. The mixing apparatuses described herein may allowfor complete and thorough mixing of these components for forming and/orcompounding a composition using a microfluidic apparatus.

Thus, the mixing methods and apparatuses described herein may be used togenerate therapeutics at rapid cycle times at high degree ofreproducibility. Thus, the mixing methods and apparatuses describedherein may allow a microfluidic apparatus to provide, in a singleintegrated apparatus, synthesis, purification, and compounding of one ormore therapeutic compositions (including, but not limited to therapeuticpolynucleotides). All or some of these processing steps may be performedin an unbroken fluid processing pathway, which may be configured as oneor a series of consumable microfluidic device(s), which may also bereferred to as a microfluidic path chip, microfluidic path plate,process chip, biochip, or process plate. This may allow forpatient-specific therapeutics to be synthesized, including compounding,at a point of care (e.g. hospital, clinic, pharmacy, etc.).

During operation of the apparatus the fluid path may remain unbroken,and contamination may be substantially eliminated by non-contactmonitoring (e.g., optically monitoring), including fluid flowmeasurement, mixing monitoring, etc. and by manipulating precisemicrofluidic amounts (metering, mixing, etc.) using pressure appliedfrom a deflectable membrane on an opposite side of the fluidic chambersand channels.

These apparatuses and methods may be configured for use at a point ofcare. For example, the methods and apparatuses described herein may beconfigured for manufacturing customized therapeutic compositionsincluding one or more therapeutic polynucleotide (e.g., mRNA, microRNA,DNA, etc.).

Thus, the methods and apparatuses described herein may provide scalablepolynucleotide manufacturing, production of single patient dosages,elimination of touchpoints to limit contamination, input and processtracking for meeting clinical manufacturing requirements, and use inpoint-of-care operations for therapeutics. The microfluidicinstrumentation and processes described herein can provide majoradvantages.

In general, the apparatuses described herein may be microfluidicapparatuses. In some examples, these microfluidic apparatuses mayinclude closed path microfluidic apparatus for processing biomolecularproducts, such as, but not limited to therapeutic polynucleotides, whichcan include mixing and formulating (e.g., combining with a selectedcarrier or vehicle) biomolecular products. These apparatuses may beconfigured to operate on one or more microfluidic device. Themicrofluidic apparatus may include one or more microfluidic device (e.g.blending chip, formulation chip, etc.).

The mixing apparatuses described herein are surprisingly effective andmay be implemented along the microfluidic flow path. These mixingapparatuses may be part of a microfluidics fluid path device that is inor between a pair of layers of material separated by a deflectablemembrane. The fluid path, including the mixing apparatus, may be formedon one side of the deflectable membrane (e.g., by forming in the firstlayer or layers on one side of the membrane, and the membrane may formthe top of the mixing apparatus; the plate on the opposite side of themembrane may be flat. In some examples the plate on the opposite side ofthe deflectable membrane may be cut-out and may form a chamber oppositeof the mixer, which may be connected to a pressure channel to allowdeflection of the membrane into the mixer and/or into the upper chamber,e.g., to drive fluid.

The mixing apparatuses described herein may include one or moreindividual mixers, which may be arranged in series and connected bychannels having a smaller height and/or width. The mixers may bereferred to as mixing components, box mixers, or vortex mixers. Examplesof these mixers are described in greater detail herein. Thus, the mixingapparatus including one or more mixers may be referred to collectivelyas a “microfluidic mixing apparatus,” a “box mixing apparatus” or“vortex mixing apparatus” or simply as a “mixing apparatus”. The mixersdescribed herein may employ vortex mixing within a vortex mixing chamber(e.g., a “box” or series of fluidly connected boxes) to efficiently mixa non-uniform incoming stream or pulse of fluid material to obtain amore uniformly mixed fluid mixture across a very small distance alongthe microfluidic flow path. This may be achieved over a wide range offluidic mixtures. One or more of the fluids to be mixed may furtherinclude particles such as nanoparticle enclosed drug substances or thelike. Efficient mixing may also be obtained over a wide variety ofratios of components entrained within the fluids introduced for mixing,as discussed in detail below. In some examples of the mixing apparatusesdescribed herein the fluid are believed to form a vortex within thechamber of the mixing apparatus, so that the direction of fluid flow maydouble back onto itself, in a circular, vortex pattern. As illustratedin the fluid modeling provided below. Thus, these mixing apparatuses maybe referred to as vortex mixers or vortex mixing chambers. It should beunderstood that referring to them mixing and mixing apparatusesdescribed herein as vortex mixing or vortex mixing chambers is notintended to limit these methods and apparatuses to a particular theoryof operation.

FIG. 1A shows a microfluidic mixing apparatus 100, having two fluidicinlet channels 103 and 105 which are offset from each other and areconfigured to transport one or more substances (e.g., biomolecularproduct(s), buffers, carriers, subsidiary components) that may becombined together. Although two inlet channels are shown, three or more(4, 5, 6, etc.) may be used, and may converge on the same mixer. Thefluids to be mixed may transit the inlet channels under positivepressure. This pressure may be constant, variable, increasing,decreasing, and/or pulsatile. The mixing apparatus is configured to bedisposed along a microfluidic flow path between an input terminus and anoutput terminus, where mixed and formulated biomolecular products may beexported from the microfluidic flow path and apparatus. The microfluidicapparatus may have a first, or upper, plate and a second, or lowerplate. The microfluidic flow path and microfluidic components (mixer,pumps, etc.) may be formed therebetween, and may be machined, molded ormanufactured in any suitable manner. The microfluidic flow path may haveone or more widths along the flow path and may have one or more verticaldimensions. Generally, the upper surface defining the microfluidic pathmay be at the same level throughout the microfluidic flow path of theapparatus.

In FIG. 1A, the microfluidic mixing apparatus receives fluid from twofluidic channels 103, 105, which may each have a width, e.g., of betweenabout 50 to about 500 μm (e.g., between about 50 to about 400, betweenabout 50 to about 300, between about 50 to about 200, about 170 μm,about 150 μm, about 110 μm, about 100 μm, about 80 μm, about 60 μm,about 50 μm, etc.). The channels may have the same width (and/orcross-sectional diameter) or may have different widths (and/orcross-sectional diameters). The channels 103, 105 may have a verticaldimension of between about 20 and about 200 μm (e.g., about 200 μm,about 175 μm, about 150 μm, about 125 μm, about 100 μm, about 75 μm,about 60 μm, about 50 μm, about 40 μm, or any value therebetween). Thetwo channels 103, 105 intersect at a fluidic intersection 109, mergingthe two streams of fluid together. The channels meet at an angle 107.The angle 107 may be less than about 180 degrees (e.g., between 5degrees and 179 degrees, between 10 degrees and 160 degrees, between 15degrees and 145 degrees, between 30 degrees and 120 degrees, etc.). Insome examples, the angle 107 may be about 30 degrees or greater (e.g.,the angle 107 may be about 35 degrees, about 40 degrees, about 50degrees, about 60 degrees, about 75 degrees, about 90 degrees, about 100degrees, about 120 degrees, about 145 degrees, about 160 degrees, or anyvalue therebetween).

The merged channel, leaving the fluidic intersection 109, may have awidth, e.g., of between about 50 μm to about 200 μm (e.g., between about50 to about 180, between about 50-150, between about 50-140, betweenabout 50-130, between about 50-120 μm, about 110 μm, about 100 μm, about80 μm, about 60 μm, or about 50 μm, etc.). The merged channel is amixing inlet channel, and may have a vertical dimension that matches oneor more (e.g., all) of the inlet vertical dimension(s), e.g., about 100μm, about 75 μm, about 60 μm, about 50 μm, about 40 μm, or any valuetherebetween. The mixing inlet channel has a first terminus comprising afluidic intersection and a second terminus comprising the opening intothe vortex mixing chamber. The mixing inlet channel enters a vortexmixing chamber 115, where the channel has a mixing inlet opening 111into the vortex mixing chamber 115 through a side wall of the vortexmixing chamber 115.

Increasing the vertical dimension 121 of the vortex mixing chamber 115so that it is greater than the vertical dimension 119 of the mixinginlet channel opening 111, and in some examples being greater than thevertical dimension 123 of the opening 113 of the mixing outlet channel,results in surprisingly enhanced mixing. FIG. 1B shows one example of amicrofluidic mixing unit 130. One example of the vortex mixing chamberprovides a common upper surface for both the mixing chamber 115 and theinlet channel opening, thus forcing the incoming fluid to dropvertically towards the lower surface. Additionally, the vortex mixingchamber 115 may be configured so that the fluid exits the vortex mixingchamber 115, at an outlet opening 113 of a mixing outlet channel. Theoutlet opening may be configured similarly to the opening 111 into themixing chamber, e.g., the vertical dimension of opening 113 in thisexample is smaller than the vertical dimension of the vortex mixingchamber 115, and may share the same upper surface as the vortex mixingchamber; the height and/or cross-sectional area of the outlet may be thesame as that of the inlet opening 111. To exit the vortex mixing chamber115, fluid is forced to move upward as well as laterally; the inlet andoutlet openings 111, 113 are also disposed on opposing sides (and inFIG. 1B on opposite walls) of the vortex mixing chamber 115. In someexamples, the openings 111, 113 are disposed vertically through the sidewalls of vortex mixing chamber 115 such that the upper limit of theopenings 111, 113 (e.g., the upper surface defining the mixing inletchannel and the mixing outlet channel) are at the same verticaldimension as the upper surface of the vortex mixing chamber 115. Theopenings 111, 113 are additionally disposed on the opposing side wallsof the vortex mixing chamber 115, offset horizontally from each other.The fluid is forced to form a vortex around a horizontal axis of the boxand mix strongly as it moves from opening 111 to opening 113 of themixing outlet channel. In general, the outlet opening is offset from theinlet opening so that the fluid will deflect from a sidewall of thechamber opposite to the inlet and deflect “down” towards the bottomsurface as part of the mixing.

In general, the vortex mixing chamber 115 has a base defining a bottomsurface, one or more side walls, and an upper surface enclosing thevortex mixing chamber. The vortex chamber may have a rectangular, oval,circular, hexagonal, etc. shape; the sidewalls may be curved (e.g.,having a radius of curvature 127 that is between 0.5 times and 0.01times the length of the shortest sidewall to which it connects). Asmentioned, a mixing inlet channel and a mixing outlet channel each openinto the vortex mixing chamber at a first and a second side wall of thevortex mixing chamber, respectively. The size of the vortex mixingchamber 115, 120 and mixing inlet/mixing outlet channels may be selectedto provide efficient mixing for a particular overall flow rate or rangeof flow rates.

In some examples, the mixing inlet channel and/or the mixing outletchannel may each have a width of between about 50 to about 200 μm (e.g.,between about 50 and 170 μm, about 170 μm, about 110 μm, about 100 μm,about 80 μm, about 60 μm, about 50 μm, etc.). The mixing inlet channeland/or the mixing outlet channel may each have a vertical dimension ofabout 75 μm, about 60 μm, about 50 μm, about 40 μm, or any valuetherebetween. In some examples, the mixing inlet channel and the mixingoutlet channel may have the same width and the same height as eachother.

A mixing assembly may include a plurality of vortex mixing chambers thatare linked together so that the inlet of the subsequent vortex mixingchamber is linked to the outlet of the prior vortex mixing chamber, asshown in FIG. 1A; a connecting channel 132 may be connected between eachvortex mixing chamber. The microfluidic vortex mixing units may have thesame shape and/or dimensions or may be different shapes and/ordimensions.

In some examples the microfluidic vortex mixing unit(s) 130 may have alength of between about 250 μm to about 1100 μm (e.g., about 300 μm,about 350 μm, about 400 μm, about 500 μm, about 600 μm, about 1000 μm,about 1100 μm, or any length therebetween). The vortex mixing chambermay have a width of between about 175 μm to about 600 μm (e.g., about200 μm, about 250 μm, about 275, about 400 μm, about 500 μm, about 600μm, or any width therebetween). In some examples, the chamber may have aheight of between about 125 μm to about 500 μm in a vertical dimension(e.g., about 125 μm, about 150 μm, about 170 μm, about 200 μm, about 250μm, about 300 μm, about 400 μm, about 500 μm, or any heighttherebetween). As mentioned, in some examples, the corners of the vortexmixing chamber may be rounded, and a corner may have a radius ofcurvature 127 of from about 50 μm to about 90 μm, or about 50 μm, about60 μm, about 75 μm, about 80 μm, about 90 μm, or any radiustherebetween. Dimensions of the vortex mixing chamber and the mixinginlet/outlet channels may be selected to allow for straightforwardmachining and minimizing the change in fluidic pressure (delta P) whilemaximizing mixing in within a small distance. Efficient usage ofmicrofluidic chip surface area also is included within the designconsiderations. For example, mixing/size selection factors may include avortex mixing chamber height that is between about 2 times and about 5times (e.g., about 2 times, 3 times, 4 times, 5 times, between about 2times-about 4 times, etc.) the height of the mixing inlet/outletchannels. In some examples, the vortex mixing chamber height is about 3times the height of the mixing inlet/outlet channels. The length of aside wall of the vortex mixing chamber may be about two or more times(e.g., about 2 times, about 3 times, about 4 times, between about 2times-about 5 times, between about 2 times-about 4 times, etc.) of thewidth of the mixing inlet/outlet channels.

In general the dimensional specifications of the mixing chambersprovided herein are exemplary; for example, the dimensions providedabove may be used for a mixer having a flow rate of between about 0.1 to10 ml/min (e.g., between about 0.2 ml/min to about 5 ml/min, betweenabout 0.5 ml/min to about 4 ml/min, etc.). The dimensions describedherein may be scaled up or down to provide larger or smaller flow rates(e.g., at different dimensional values) in order to achieve the samevertical flow (e.g., equivalent mixing) for a particular appliedpressure (e.g., between about 6.99 kPa and about 206.8 kPa). Thus, thedimensions provide herein may be scaled (e.g., scaling of thesestructures) in order to allow for different flow rates.

For example, a microfluidic mixing apparatus may include a mixing inletchannel, a microfluidic vortex mixing chamber and a mixing outletchannel, where the mixing inlet and mixing outlet channels have a widthof about 100 μm and a vertical dimension from the base of the mixinginlet/outlet channel(s) of about 50 μm; a vortex mixing chamber having alength of 350 μm, a width of 250 μm, a height of 150 μm, and a radius ofcurvature of about 75 μm at the rounded corners of the chamber. Themixing inlet opening 111 is therefore offset along the 350 μm long sidewall horizontally away from the mixing outlet opening 113 along theopposite 350 μm long side wall by up to about 150 μm.

In another example, a microfluidic mixing apparatus may include a mixinginlet channel, a microfluidic vortex mixing unit and a mixing outletchannel, where the mixing inlet and mixing outlet channels may have awidth of about 150 μm and a vertical dimension from the base of themixing inlet/outlet channel(s) of about 50 μm; a vortex mixing chamberhaving a length of 500 μm, a width of 250 μm, a height of 150 μm, and aradius of curvature of about 75 μm at the rounded corners of thechamber. The mixing inlet opening 111 is therefore offset along the 500μm long side wall horizontally away from the mixing outlet opening 113along the opposite 500 μm long side wall by up to about 200 μm.

As mentioned, a vortex mixing unit 130 may be disposed along themicrofluidic flow path paired with a second (or more) vortex mixingunit, similarly to the pair of vortex mixing units shown in FIG. 1A. Thesecond vortex mixing unit may be configured similarly to the firstvortex mixing unit. That is, vortex mixing chamber 115 and 120 may havethe same dimensions as each other, to provide similar vortexing andmixing characteristics as desired above. For example, the respectivemixing inlet and outlet channels may be related as follows: the firstmixing outlet channel of the first vortex mixing unit may have a firstterminus including the opening 113 into the first vortex mixing chamber115 and a second terminus including the second mixing inlet channelcomprising the opening 131 into the second vortex mixing chamber 120 ofthe second vortex mixing unit. The second mixing outlet channel, e.g.,of the second vortex mixing unit, has a first terminus at the opening133 into the second vortex mixing chamber 120, and a second terminus atthe outlet 117 from the mixing apparatus, along the microfluidic path.The pair of two microfluidic vortex mixing units may be designed tominimize the pressure drop (Delta P) and for a smaller pair of mixingunits having a vortex chamber with a 350 μm length, 250 μm width, and150 μm height, as described above, the Delta P per pair at a 0.5 ml/minflow rate is about 10.3 kPa (e.g., between about 6.9 kPa and about 206.8kPa, between about 6.9 kPa and about 172.4 kPa, between about 6.9 kPaand about 106.0 kPa, between about 6.9 kPa and about 103.4 kPa, betweenabout 6.9 kPa and about 68.9 kPa, between about 6.9 kPa and about 34.5kPa, etc.). A pair of vortex mixing units having the larger dimensionwhere the chamber is 500 μm long, 250 μm wide and 150 μm deep, has aDelta P at a 1 ml/min flow rate of about 2.4 psi (16.5 kPa).

In some examples, a third or fourth microfluidic vortex mixing unit(s)may be included along the microfluidic flow path, as shown in FIG. 3A,to provide a two-stage mixing apparatus. The first chained group ofmixing units 330 is a first stage; this mixed product may then becombined with a second group of mixing units 331 at a second stage. Theadditional microfluidic vortex mixing units may be configured like themicrofluidic vortex mixing units described above. Generally, eachindividual vortex mixing unit may have the same features and dimensions,or different dimensions. In FIG. 3A, the first stage 330 includes fourmixing units (e.g., two pairs of mixing units) that may be connected asshown. For example, a second terminus of the second mixing outletchannel is continuous with a third mixing inlet channel and an openinginto a third vortex mixing chamber. A third mixing outlet channel mayhave a first terminus that includes an opening into the third vortexmixing chamber and a second terminus that may be the fourth mixing inletchannel and an opening into a fourth vortex chamber. A fourth mixingoutlet channel may have a first terminus that may be an opening into thefourth vortex mixing chamber and a second terminus that may be an outputfrom the microfluidic mixing apparatus.

Returning now to FIGS. 2A-2C, FIG. 2A shows flow trajectory modellingfor the microfluidic mixing apparatus 200, which is similar to themixing apparatus 100 of FIG. 1A, having one pair of microfluidic vortexmixing units 130, and demonstrates the mixing capability of themicrofluidic mixing apparatuses (showing mixing of equal parts ethanol(arrows 255) and water (arrows 257), by mixing fraction). The shading ofthe arrow indicates the mixing fraction. In FIG. 2A the perspective flowmodel for a 1:1 mixture of ethanol, introduced at the first inlet 203,and water, introduced at the second inlet 205. The volume fraction ofethanol to water along the microfluidic flow path shown by the arrowsindicates substantial mixing in the vortex mixer. Inlet 203 is labeledto represent the 100% volume ethanol fraction, while second inlet 205 islabeled to show that there is no ethanol present. At fluidicintersection 209, the flows are moving laminarly without much mixing, asindicated by region 204, which shows distinct and unmixed ethanol andwater flow. However region 206, encompassed by the white oval, showsabrupt change of concentration of ethanol as the fluid flow cascadesdown into vortex mixing chamber 215 (which may be like 115, 120 ofgeneric microfluidic vortex mixing unit 130), where the aqueous edge ofthe flow is now about 0.1667 fraction of ethanol (v/v). As the flowreaches the mixing outlet opening region 208, the flow now containsnearly an equivalent volume fraction of ethanol, and the rest of theflow (arrows 259) within region 212 is a 0.5000 mixture (v/v) ofethanol. FIG. 2B shows a representation for a similar experiment,showing a side view within both a first and a second vortex mixing unit(215, 220) along the microfluidic path, both of which may be like 115,120 of generic microfluidic vortex mixing unit 130. The side view ofFIG. 2B more clearly shows the vortexing movement that the fluid isforced to flow in, in order to exit the vortex mixing chamber 215. Theflow of 1:1 ethanol:water v/v can be shown to be substantially mixed tosomewhere between 0.4167 to 0.5833 ethanol/water v/v at the opening 211of the mixing outlet channel from the vortex mixing chamber 215. In thisexample, there is a small region at 214 where volume fraction as high as0.667 still is present, but throughout most of region 216, the 0.4167 to0.5833 ethanol/water v/v ratios are predominant. A second vortex mixingunit 226 may be used for final mixing within vortex mixing chamber 220to produce thoroughly mixed ethanol/water at the second output 217 fromthe pair of microfluidic vortex mixing units. Within the vortex mixingchambers, the arrangement of the chamber allows for mixing in which theflow is directed down towards the bottom of the chamber, as shown inFIG. 2B. As will be described in greater detail below, the enhancedmixing temperature may be determined by calibrating the geometry, andparticularly the depth of the chamber, and the flow rate, permittingnearly complete mixing in a single vortex mixing chamber.

Another flow modelling example is shown in FIG. 2C, showing a ratio of1:10 ethanol (input at inlet 203) to water (input at inlet 205). Theshading indicates the fraction of ethanol to water (per scale). Region218 shows the side-by-side flow of ethanol/water where the volumefraction of ethanol is already reduced to between 0.7500 to 0.4167, asthe flow starts to cascade down into the vortex mixing chamber 215.Region 220 shows a portion of the flow having a slightly elevated volumefraction of ethanol between 0.1667 to 0.2500, but at the point ofexiting the second vortex mixing chamber 220, the volume fraction ofethanol 263 has been completely equilibrated, and is outputted from themicrofluidic mixing apparatus at 217. The arrangement of the mixinginlet opening, mixing outlet opening, vortex mixing chamber as shownprovides a mixing apparatus that is substantially insensitive to theratio of the fluids being mixed, as both a 1:1 ratio and a 1:10 ratio offluids in the two inlet channels are brought to an equilibrated mixtureupon exiting the mixing apparatus at 217.

FIGS. 2D-2J illustrate examples of other vortex mixing apparatusesshowing the effects of examples in the configuration of the vortexmixing chamber on total mixing at exemplary pressures and flow rates.

For example, FIGS. 2D-2E show an example of an apparatus including aseries of vortex mixing chambers in which each of the channel inlets 211is 100 μm wide by 50 μm deep. The depth is measured from the top surface(e.g., top plate), and the vortex mixing chamber is approximately square(with rounded sides), having a length that is 250 μm, a width of 250 μmand a depth of 100 μm. Thus, in this example, the depth of the vortexmixing chamber is 2 times the depth of the inlet, where the inletopening and the chamber have a common upper surface, so that the maximumdrop from the inlet opening to the top (or bottom, depending on theframe of reference) of the vortex mixing chamber is approximately thesame as the depth of the inlet. In this case, as shown by the shadedarrows, for a 1:10 mixture of ethanol:water, mixing is not completeafter the second sequential vortex mixing chamber 226 (connected inseries). FIG. 2E shows the pressure drop for the same example (showingsix sequentially connected vortex mixing chambers). Mixing issubstantially complete by the third mixing chamber. The pressure dropsfrom each of the water 205 and ethanol 203 supply channels of about 20.3lbf/in², dropping by about 0.76 lbf/in² between each sequential vortexmixing chamber.

FIGS. 2F and 2G show another example of an apparatus including a seriesof vortex mixing chambers in which each of the channel inlets 211 isalso (as in FIGS. 2D-2E) 100 μm wide by 50 μm deep. The vortex mixingchamber in this example is approximately rectangular (with roundedsides), having a length that is 350 μm, a width of 250 μm and a depth of100 μm. Thus, this example has vortex mixing chambers that are 1.4 timesas long but are otherwise similarly dimensioned as shown in FIGS. 2D and2E, above. In FIGS. 2F and 2G the depth of the vortex mixing chamber isalso 2 time the depth of the inlet, where the inlet opening and thechamber have a common upper surface, so that the maximum drop from theinlet opening to the top (or bottom, depending on the frame ofreference) of the vortex mixing chamber is approximately the same as thedepth of the inlet. The mixing profiles for 1:10 ethanol:water (shown bythe shaded arrows) is nearly the same as in the example of FIGS. 2D and2E. FIG. 2G shows the pressure drop for the same example (also showingsix sequentially connected vortex mixing chambers). Mixing issubstantially complete after leaving the second mixing chamber. Thepressure drops from each of the water 205 and ethanol 203 supplychannels of 20.19 (e.g., 20.19 lbf/in² and 20.19 lbf/in²), dropping byabout 0.75 lbf/in² between each sequential vortex mixing chamber.

FIGS. 2H and 2I show an example of an apparatus including a series ofvortex mixing chambers in which each of the channel inlets 211 is also(as in FIGS. 2D-2G) 100 μm wide by 50 μm deep. The vortex mixing chamberin this example is approximately rectangular (with rounded sides),having a length that is 500 μm, a width of 250 μm and a depth of 100 μm.Thus, this example has vortex mixing chambers that are twice as long butare otherwise similarly dimensioned as shown in FIGS. 2D and 2E, above.In FIGS. 2H and 2I the depth of the vortex mixing chamber is also 2times the depth of the inlet, where the inlet opening and the chamberhave a common upper surface, so that the maximum drop from the inletopening to the top (or bottom, depending on the frame of reference) ofthe vortex mixing chamber is approximately the same as the depth of theinlet. The mixing profiles for 1:10 ethanol:water (shown by the shadedarrows) is nearly the same as in the example of FIGS. 2D and 2E. FIG. 2Ishows the pressure drop for the same example (also showing sixsequentially connected vortex mixing chambers). Mixing is substantiallycomplete after leaving the second mixing chamber. The pressure dropsfrom each of the water 205 and ethanol 203 supply channels of about 20(e.g., 20.33 lbf/in² and 20.37 lbf/in²), dropping by about 0.75 lbf/in²between each sequential vortex mixing chamber.

FIG. 2J shows an example of an apparatus including a series of vortexmixing chambers in which each of the channel inlets 211 are again, asshown in FIGS. 2D-2I, 100 μm wide by 50 μm deep. The vortex mixingchamber in this example is approximately rectangular (with roundedsides) but is nearly 3 times as deep as the channel inlet opening. InFIG. 2J, the vortex mixing chamber has a length that is 350 μm, a widthof 250 μm and a depth of 150 μm. Thus, this example has vortex mixingchambers that have a similar shape to those shown in FIGS. 2F-2G buthave a depth that is 50% larger. Thus, in FIG. 2J the depth of thevortex mixing chamber is 3 times the depth of the inlet, where the inletopening and the chamber have a common upper surface, so that the maximumdrop from the inlet opening to the top (or bottom, depending on theframe of reference) of the vortex mixing chamber is approximately 2times the depth of the inlet. The mixing profiles for 1:10 ethanol:water(shown by the shaded arrows) show that the mixing in this example atthese pressures and flow rates are highly efficient, showing nearlycomplete mixing after the first vortex mixing chamber, as shown by thearrows indicating the volume faction of ethanol. The pressure dropbetween vortex mixing chambers is approximately the same as shown inFIGS. 2D-2I. Thus, at these pressures and flow rates, the relative dropfrom the inlet into the vortex mixing chamber appears to stronglycorrelate with mixing efficiency, as compared, e.g., to chamber length.In the mixing model of FIG. 2J, the vorticity and complete mixing wasachieved in one stage.

Any of the vortex mixing chambers described herein may be part of amicrofluidic mixing apparatus; a microfluidic mixing apparatus mayinclude one or more vortex mixing chambers. A microfluidic mixingapparatus may be implemented as part of a microfluidic device. Forexample, a microfluidic mixing apparatus used as part of a microfluidicapparatus for mixing and formulating biomolecular products is shown inFIGS. 3A-3E and 4. As mentioned above, the microfluidic apparatus may beformed from a first plate and a second plate, and the microfluidic flowpath may be formed in portions of one or both plates. In FIG. 3A, themicrofluidic apparatus 300 may include an elastic layer disposed betweenthe first plate and the second plate. This apparatus also includes twomixing regions 330, 331, and is configured to mix materials from threedistinct inputs 303, 305, 335. Similar to the mixing apparatusesdescribed above, a first fluid is introduced to a first fluidic input303 and a second fluid is introduced into a second fluidic input 305,which intersect at fluidic intersection 309, which may be configuredlike fluidic intersection 109. The fluids may be configured to be drivenat a pressure greater than atmospheric pressure, assisted by inletvalves 332 (e.g., where positive or negative pressure may be applied).The merged flow continues into four vortex mixing chambers 330, arrangedsequentially along the microfluidic flow path. Each of the individualvortex mixing chambers of the mixing apparatus 330 may be configuredlike microfluidic vortex mixing unit 130 describe above and may have anyof the dimensions as described above. The two-stage mixing apparatus maybe configured to output the mixed fluid via a single output from thefinal microfluidic vortex mixing chamber (the fourth in the series).

Apparatus 300 is further configured to mix a third fluidic component.After outputting the mixed fluid from the first stage mixing apparatus330, the output channel becomes a third fluidic inlet 333 and intersectswith a fourth fluidic inlet 335, introducing the third fluidic componentat a second fluidic intersection 319, as described above. The mergedfluid flow is then input into a vortex mixing chamber of the secondmixing stage 331, which is disposed sequentially along the microfluidicflow path. Each of the vortex mixing chambers of this second stage 331may be configured like any of microfluidic vortex mixing chambersdescribed above. Complete mixing may be achieved using a single vortexmixing chamber in either the first or second stage mixing paths, howeverin some examples the additional mixing chambers may allow furthermixing, and may provide a buffer for examples in flow rate. The mixedfluid from traversing through the vortex mixing chambers may be outputin a single channel from the mixing pathway (e.g., from the secondstage), and may continue along the microfluidic flow path for furtherprocessing in other regions of the microfluidic apparatus.

The microfluidic path apparatus 300 in FIG. 3A also includes vacuum caps334, which may be held at negative pressure to remove gas from theliquid (fluidic) lines by drawing it through the membrane overlying thefluid path if it is gas permeable. PolyDiMethylSilicone (PDMS) elastomerfilm for example is sufficiently gas permeable to allow this. For thecascaded mixing apparatus shown in this example, there are three fluiddriving chambers configured to drive each of the first, second and thirdfluidic components into the respective inlet channels. Each fluiddriving chamber has a fixed volume and is formed between the first plateand the second plate. A portion of the elastic layer disposed betweenthe first and the second plate, divides each fluid driving chamber intoa fluid-contacting side in the second plate and a pressure-receivingside in the first plate. The pressure-receiving side may be pressurizedto drive fluidic through the chamber and into the mixing apparatuses330, 335. The fluid driving chambers each include a fluid port (from themicrofluidic flow path) that fluidly connect with the fluid-contactingside of each of the respective first and second fluid driving chambersvia a respective fluid channel in the second plate; and a pressure portextending through the first plate and into the second plate that fluidlyconnect with the pressure-receiving side of the fluid driving chambervia a respective pressure channel extending through the second plate andalong the first plate. The volume of the fluid-contacting side of thefluid driving chamber may be adjusted by applying pressure or vacuumfrom the respective pressure port. The fluidic port of the fluid drivingchamber may further include a flow restrictor 336. In some examples, theflow restrictor may include a serpentine elongate fluidic channel.

In general, the methods and apparatuses described herein may include theuse of multiple fluids (e.g., materials in fluids, including mRNA,buffers, salts, delivery vehicles, etc.) that may be supplied fromexternal reservoirs. Any of these methods and apparatuses may includeone or more vacuum cap structures and valves to advance all fluids to astarting point, without bubbles, then release the fluids in a controlledway such that the mixing results are stable over the time of mixing. Asmentioned above, the vacuum cap may be configured to reduce or removebubbles from the fluid(s). The apparatuses and methods described hereinmay also include valves connecting to one or more waste collectionregions. In some examples the initial results may be sent to wasteoutput if needed to preserve the quality of the overall output.

The microfluidic mixing apparatus 300 may further include a fourth fluiddriving chamber which may be disposed along the microfluidic flow path,subsequent to the mixing apparatus. In FIG. 3A, a vacuum cap 338 may beincluded. While two cascaded mixers are shown, additional mixers may beincluded as part of the fluid channel. In this manner the steps offorming a nanoparticle based therapeutic may be broken down into stepsthat are accomplished in a very timely and controlled manner along thecascade. For example in the first mixer a polynucleotide such as mRNA inwater, may be mixed with a delivery vehicle molecule or molecules inethanol to form complexed nanoparticles. A second mixer may be used toadd a dilution agent such as a citrate-based buffer solution for pHadjustment. If more mixers are used additional steps could be included.For example it may be desirable to add a surface layer to thenanoparticles formed in the first mixing step to enhance bioactivity ofthe nanoparticles. This could be done by combining the output fluidstream of the first mixer with a solution containing the desiredovercoating material in a second mixing structure. This could then becombined in a third mixer with a pH adjustment buffer solution. It mightalso be useful to create the mixture of polynucleotides and water in anupstream mixer structure where the polynucleotides and Delivery vehiclemolecules are combined. In this way more concentrated polynucleotides asare typically produced in the mRNA production process could be dilutedevenly with water prior to the nanoparticle formation step. Similarlyupstream mixing of Ethanol and delivery vehicle molecules could be donebefore the mixer that combined the polynucleotide solution and deliveryvehicle solution.

FIGS. 3B and 3C illustrate an example of a microfluidic apparatusconfigured as a continuous mixer. In FIG. 3B, the microfluidic apparatus350 includes a plurality of mixers arranged in parallel. As describedabove, the microfluidic apparatus may include two or more plates,separated by a deflectable membrane, with chambers and channels formedin the upper and/or lower surfaces of plates, which may be divided bythe membrane. In this example, the apparatus may be configured toreceive multiple reagents, e.g., mRNA, delivery vehicle, diluent, etc.,that may be directly pumped from reagent containers (e.g., vials, tubes,not shown) that are outside of the microfluidic apparatus (e.g.,“chip”). The mixer may be used to mix the reagents for dispensing off ofthe microfluidic apparatus, e.g., into a collection container (notshown). The microfluidic device may include ports for coupling to one ormore pressure lines 352 that may be used to selectively apply pressure(e.g. positive and/or negative air pressure) to control one or morevalves (e.g., allowing flow of the reagents on/off the chip). Thereagents may be pressurized within the reagent containers, driving themonto the microfluidic apparatus if a valve allowing them to flow isopened.

FIG. 3C shows an enlarged view of region D of the apparatus 300 of FIG.3B. In this example, the mixer 369 may be configured as a single mixeras describe herein. Three inputs for each of three reagents are shown,and include an mRNA input 355, a delivery vehicle input 357 and adiluent input 359. A valve 363 may be opened/or closed by selectivelyapplying positive and/or negative pressure (e.g., by a controller) toallow fluid to flow. In the example shown in FIG. 3C, each reagent isalso coupled to a vacuum cap 361 that may be used to remove air (e.g.,bubbles) from the fluid before it is passed into the mixer 369. Forexample, the vacuum cap may apply negative pressure to draw air througha membrane that allows passage of air but not fluid.

In FIG. 3C the mixer 369 includes a first fluidic input 365 and a secondfluidic input 367 that meet at a fluidic intersection channel thatinputs into the mixer 369. In this example, the mRNA reagent is mixedwith the delivery vehicle in the mixer, as described above. The outputof the mixer forms an intersection with an input 371 for dilutionbuffer, just upstream of the output 354 of the microfluidic device(“chip”).

In this example, the mixer may be operated continuously or nearlycontinuously, as the volume of material arrives from an off-chipcontainer and the output from the chip may be stored in an off-chipstorage container. Thus, in this example, fluid may be driven throughthe mixer directly by applying air pressure. In some cases, which may beused for smaller volumes, or more discrete (including metered) volumesof material, the fluid may be driven through the channels and/or mixerby defecting the membrane between plates of the microfluidic device.

The example, shown in FIG. 3C may be configured to prevent clogging ordeposition of material within the mixer, which is described in greaterdetail below in reference to FIG. 8. For example, FIGS. 3D and 3Eillustrate examples of microfluidic apparatuses similar to that shown inFIGS. 3B and 3C, in which dilution buffer is added (with or withoutmixing using a mixer) to a mixed solution of reagents, e.g., mRNA anddelivery vehicle, following mixing in a mixing chamber. In FIG. 3D theoutput channel 373 of the mixers 369, 369′, 369″ extends only a veryshort distance (e.g., less than about 100 μm, less than about 150 μm,less than about 200 μm, less than about 400 μm, less than about 500 μm,etc.) before intersecting with the dilution buffer input 371. Incontrast, in FIG. 3E, the microfluidic apparatus is configured so thatthe output channel 373′ of the three, serially-arranged mixers 369,369′, 369″ if long, e.g., greater than about 600 μm, greater than about700 μm, greater than about 800 μm, greater than about 900 μm, greaterthan about 1000 μm, etc.

Apparatuses in which the output channel is shorter than, e.g., 500 μm(about 400 μm, about 300 μm, etc.) may generally be more compact thanother designs while still providing enhanced mixing. Further, lessdeposition of material may result when mixing with dilution buffer avery short distance from the input. Alternatively or additionally,shortening the distance between the first 369″ and the second 369′ mixer(or the second and the third 369) may also reduce or eliminatedeposition. For example, the mixing apparatuses described herein mayinclude less than about 500 μm (e.g., less than about 400 μm, less thanabout 300 μm, less than about 200 μm, less than about 100 μm) betweenserially arranged mixing chambers. In some examples, these apparatusesmay include a dilution buffer input at or near the output of the mixingapparatus.

FIG. 4 shows an example of portion of another microfluidic device alsopressure drops across the apparatus 400, including a mixing sub-assembly433 which is configured like apparatus 300. A first fluid component maybe introduced into the microfluidic device at input 403′. In thisexample, the fluid flow is initiated at a pressure of 23.28 lbf/in²(160.5 kPa), and traverses through a flow restrictor 434, and vacuum cap435, arriving at first fluidic inlet 403 at a pressure of 20.15 lbf/in²(138.9 kPa). The second fluid component is introduced at input 405′ at apressure of 23.30 lbf/in² (160.6 kPa), flowing through its respectiveflow restrictor and fluid driving chamber, to the second fluidic inlet405 at a pressure of 20.17 lbf/in² (139.0 kPa). The two fluidsintersect, at an equalized pressure, and are mixed in the first vortexmixing chamber, and may pass into subsequent sequentially arrangedchambers of the mixing sub-assembly 433 until exiting at output 417,e.g., at 16.73 lbf/in² (115.3 kPa). The mixture may then enter a secondstage 445 of the cascaded mixing apparatus, to intersect a third fluidiccomponent at the second fluidic intersection. The third fluidiccomponent in this example is input into the microfluidic path apparatus400 at input 407, e.g., at a pressure of 23.30 lbf/in² (160.6 kPa), andtraverses a flow restrictor 457 and to arrive at the fourth fluidicinlet 435 at 16.73 lbf/in² (115.3 kPa), pressure equalized to the fluidarriving from the third fluidic inlet 417. The merged flow passesthrough the last pair of vortex mixing chambers of the second stage ofthe mixing sub-assembly and enters a 438 at 14.36 lbf/in² (99.0 kPa).Pressure may be further reduced within 438, and fluid may be outputtedat output 414, e.g., at a pressure of 7.60 lbf/in² (52.4 kPa). In someexamples this mixing subassembly may be fluidly connected in-line withadditional processing components, either on the same microfluidic device(microfluidic path apparatus) or a separate microfluidic device.

In general, the mixers described herein may be cascaded together.Cascaded mixers may provide additional mixing and may allow high degreesof mixing at increased flow rates. For example any of the microfluidicapparatuses described herein may include a plurality of cascadingmicrofluidic vortex mixing apparatuses, wherein each microfluidic vortexmixing apparatus comprises: a vortex mixing chamber comprising a basedefining a bottom surface, side walls, and an upper surface enclosingthe vortex mixing chamber; a mixing inlet channel comprising an openinginto the vortex mixing chamber at a first side wall of the vortex mixingchamber; a mixing outlet channel comprising an opening into the vortexmixing chamber at a second side wall of the vortex mixing chamber,wherein a vertical dimension of the vortex mixing chamber is larger thana vertical dimension of the mixing inlet channel and is larger than avertical dimension of the mixing outlet channel; further wherein theplurality of microfluidic vortex mixers are connected in a series sothat the mixing inlet channel of each of the microfluidic vortex mixersafter a first microfluidic vortex mixer in the series is connected tothe mixing outlet of a prior microfluidic vortex mixer in the series.

For example, FIG. 5 shows a microfluidic device configured as amicrofluidic path formulation apparatus 500 including a cascading mixingsub-assembly 510 similar to that shown in FIG. 4. This mixingsub-assembly may include a plurality of vortex mixing chambers, whichare configured in series. Apparatus 500 also includes pumps 520 and 550,and fluid driving chambers 530, 540, 560 (which may act as blendingchambers).

Temperature

In any of the mixing apparatuses described herein Applicants havesurprisingly found it to be beneficial for some materials, e.g., mRNA inaqueous solution and delivery vehicle (e.g., in ethanol) to mix at atemperature that is less than room temperature (e.g., less than about 25degrees C.), such as, for example, 20 degrees C. or less, 18 degrees C.or less, 15 degrees C. or less, 12.5 degrees C. or less, 10 degrees C.or less, 8 degrees C. or less, 7 degrees C. or less, etc., e.g., between20 and 5 degrees C., about 10 degrees C., etc.).

Any of the microfluidic path apparatuses described herein may beoperated as part of a system that includes temperature control,including temperature control of the mixing portion (mixingsub-assembly) of a microfluidic device. Thus, the mixing sub-assembly,including one or more vortex mixing chambers, may be cooled to atemperature, e.g., between 20 degrees and 5 degrees C., such as betweenabout 18 degrees and 5 degrees C., between about 15 degrees C. and 5degrees C., between about 15 degrees C. and 8 degrees C., etc.) duringoperation of the mixing sub-assembly.

In some examples the entire microfluidic device including the mixingchamber may be regulated to the mixing temperature. Alternatively only aportion of the microfluidic device may be temperature controlled asdescribed herein. For example, just the mixing chamber(s) may betemperature controlled to the mixing temperature, other portions of themicrofluidic devices may be temperature controlled to one or moredifferent temperatures. In some examples, the microfluidic device (orany sub-region thereof, such as the mixing chamber(s)) may betemperature controlled to the mixing temperature only while mixing; atother times they may be held at another temperature.

FIG. 6 is a graph illustrating the effect of temperature on mixing usinga mixing apparatus as described herein. In FIG. 6, mixing using a mixingapparatus similar to that shown above in FIGS. 1A-1B is shown(corresponding to the “8/28 Box” mixing), and compared against unmixed(“Cells alone”) and hand mixed (“8/28 Hand”) samples. Samples includedcells that were transfected with a fluorescing agent, allowingquantification of the efficacy of mixing; a greater florescent signalindicates a higher degree of mixing efficiency, measured as correctedbioluminescence (RLU). Reagents mixed by hand (“8/28 Hand Master,” “8/28Hand Aliquot 1” and “8/28 Hand Aliquot 2”) had a correctedbioluminescence that was approximately equivalent to those mixed at 21degrees C. in a mixing apparatus as described above (e.g., “8/28 Box 21C1,” “8/28 Box 21C 2,” “8/28 Box 21C 3” and “8/28 Box 21C 4”).Surprisingly, those mixed at lower temperatures, e.g., 10 degrees C.,showed a much higher degrees of bioluminescence (compare with “8/28 BoxRun 7 10C” and “8/28 Box Run 8 10C”). In FIG. 6, those mixed with thesame mixing apparatus at lower temperature, e.g., 10 degrees C., hadalmost twice the bioluminescence as compared to the same mixingapparatus or by hand at 21 degrees C. For the combination of reagentsshown, at higher temperatures (e.g., 40 degrees C. and 60 degrees C.),the bioluminescence, was approximately the same as at 21 degrees C.

The mixing temperature may be manually or automatically set. In someexamples, the mixing temperature, which is typically but not exclusivelybetween about 20 degrees and about 5 degrees C., may be determined basedon the mRNA (e.g., the therapeutic mRNA) and/or delivery vehicle that isbeing mixed. For example, the combination of mRNA and delivery vehiclemay be used to determine the enhanced mixing temperature, as describedabove. The enhanced mixing temperature may be determined empirically(e.g., experimentally) and/or by calculating, e.g., based on the size,molecular weight, sequence, etc. of the mRNA and/or delivery vehicle.

As described above, the mixing apparatuses described herein may be partof a microfluidic apparatus (e.g., a microfluidic device), and mayinclude a first fluidic input and a second fluidic input, a fluidicintersection channel configured to receive fluid from the first fluidicinput and the second fluidic input, in which the fluidic intersectionchannel opens into a first mixing chamber on an upper region of a firstside of the first mixing chamber. The first mixing chamber may have adepth that is greater than about 1.5 times a depth of the fluidicintersection channel. The device may also include an outlet channel onan upper region of a second side of the first mixing chamber, whereinthe outlet channel has a depth that is less than the depth of the firstmixing chamber, further wherein an opening of the outlet channel isoffset along a width of the second side of the first mixing chamberrelative to the fluidic intersection.

In some examples, multiple mixers (e.g., multiple mixing chambers) maybe included as part of the microfluidic mixing apparatus and may beconnected in series. For example, FIGS. 7A-7D illustrate examples ofmixing apparatuses having one (FIG. 7A), three (FIG. 7B), six (FIG. 7C)and twelve (FIG. 7D) mixing chambers. As described above, surprisingly,nearly uniform mixing may be achieved with a single mixing chamber (see,e.g., FIGS. 2A-2E). In some cases, particularly where the mixtureincludes particles that are suspended in the fluid being mixed, morethan one, e.g., two or three, mixing chambers may be used to achievecomplete or nearly complete mixing. This is illustrated below, and isparticularly surprising, given the relatively small dimensions (e.g.,footprint) for the mixing apparatus, even when relatively high flowrates and low pressures are used (e.g., pressures of between about 6.9kPa to about 206.8 kPa and flow rates of between 1 ml/min and about 10ml/min). The mixing apparatuses described herein may have a total lengthof about 2 mm or less (e.g., about 1.75 mm or less, about 1.7 mm orless, about 1.6 mm or less, about 1.5 mm or less, about 1.4 mm or less,about 1.2 mm or less, about 1 mm or less, about 0.8 mm or less, about0.7 mm or less, etc.) from input to output. Even these relatively shortlengths may achieve mixing that is nearly uniform.

All of the apparatuses and methods described herein provide mixing thatis superior to that of hand mixing, including providing more uniformityas well as smaller resulting particle sizes in mixtures includingparticles (which may otherwise cluster). However, mixtures havingparticles may present particular challenges for microfluidic mixing. Forexample, repeated and/or continuous use of a microfluidic mixer mayresult in deposition of particles within the channels of themicrofluidic mixing apparatus. FIG. 8 illustrates this potential issue.In FIG. 8, an image of a mixing apparatus is shown. The mixing apparatusinclude three serially connecting mixers (mixing chambers) as describedherein, e.g., having a width/depth/length of about 250/200/500 μm. Inthis illustration the mixing apparatus was used for continuousoperation, mixing fluids including material (e.g., mRNA and molecules ofdelivery vehicle with or without mRNA, such as molecules of anamino-lipidated peptoid delivery vehicle) to form therapeutics (e.g.,mRNA encapsulated in delivery vehicle), but resulted in deposition ofmaterial 807 within the mixing apparatus over time. In operation, suchdeposition may lead to clogging. The apparatuses and method describedherein may be configured to reduce or prevent clogging and/or depositionof material.

For example, in some examples the number of mixing chambers may belimited. Thus in some cases 3 or fewer mixing chambers may be used. Asmentioned and illustrated above, in some examples two mixing chambersmay be serially coupled for mixing in a mixing apparatus. In someexample, three mixing chambers may be serially coupled for mixing in themixing apparatus. Alternatively, in some examples only a single mixingchamber may be included. These configurations may have the added benefitof having a substantially smaller footprint as compared to other mixers.

In some examples, the size of the chambers and/or channels of the mixingapparatus may be proportionally increased. Larger mixing chambers mayreduce the deposition of particles within the channels. For example, insome examples, the dimensions of the mixing chamber(s) may have a widthof between about 225 and about 600 μm (e.g., between about 250-about 600μm, between about 300-about 550 μm, etc.), a depth of between about 175and about 425 μm (e.g., between about 200-about 400 μm, between about300-about 425 μm, etc.), and a length of between about 450-about 1050 μm(e.g., between about 500 μm-about 1000 μm, etc.). For example, themixing chamber(s) may have a width/depth/length of about 500/400/1000μm. Similarly, the connecting channel(s) may have a width of betweenabout 75 μm-about 225 μm (e.g., between about 100 μm-about 200 μm,etc.), a depth of between about 75 μm-about 225 μm (e.g., between about100 μm-about 200 μm, etc.), and a length of between about 225 μm-about525 μm (e.g., between about 250 μm-about 500 μm, etc.).

FIGS. 9A and 9B illustrate examples of mixing apparatuses that aresimilar but scaled relative to each other. The mixing apparatus of FIG.9A shows mixing chambers 905 and connecting channels 903 that are of afirst set of dimensions (e.g., the mixing chamber width/depth/length isabout 250/200/500 μm, and the connecting channel width/depth/length isabout 100/100/250 μm). In FIG. 9B the same shape has been scaled up by afactor of 2 (e.g., 2 times), so that the mixing chamber and connectingchannels have twice the width, depth and length (e.g., mixing chamberhaving a width/depth/length of about 500/400/1000 μm, and connectingchannels having width/depth/length of about 200/200/500 μm).

As shown in FIG. 9C, the overall mixing efficacy of the mixing apparatusin both the smaller (e.g., FIG. 9A) and larger (e.g., FIG. 9B)dimensions were comparable; both the average particle size as well asthe dispersity of the particles was examined for both. Dispersity is ameasure of the heterogeneity of sizes of molecules or particles in amixture. A collection of objects is called uniform if the objects havethe same size, shape, or mass. A sample of objects that have aninconsistent size, shape and mass distribution is called non-uniform.Polydispersity index (PDI) is used as a measure of broadness ofmolecular weight distribution, therefore an indicator of the sizedistribution. The larger the PDI, the broader the molecular weightdistribution. PDI of a polymer is calculated as the ratio of weightaverage by number average molecular weight. Dispersity (e.g., PDI) canbe measured by light scattering measurements such as dynamic lightscattering, and/or direct measurement, e.g., via mass spectrometry,using matrix-assisted laser desorption/ionization (MALDI) orelectrospray ionization with tandem mass spectrometry (ESI-MS). ThePolydispersity Index is dimensionless and scaled such that valuessmaller than 0.05 are rarely seen other than with highly monodispersestandards. Values greater than 0.7 may indicate that the sample has avery broad size distribution, and thus not uniform in size. TheZ-Average size or Z-Average mean may be used in dynamic light scatteringas a parameter (also known as the cumulants mean) to provide ahydrodynamic parameter that is applicable to particles in a dispersionor molecules in solution.

As shown in FIG. 9C, the PDI for both the smaller (FIG. 9A) and larger(FIG. 9B) mixing apparatuses were reasonably similar; however, theZ-average was somewhat smaller in the smaller mixer apparatus ascompared to the larger mixing apparatus.

Any of the mixing apparatuses described herein may have rounded orcurved corners and/or edges. For example, FIG. 10A shows a mixingapparatus similar to that shown above (e.g., FIG. 7B, 9A, etc.) and FIG.10B shows an example of a mixing apparatus having rounded edges 1015and/or corners on the bottom and/or top of the mixing apparatus. Rounded(e.g., radiused, curved, etc.) edges/corners may prevent dead regions orregions of stagnation in the mixer where particles may deposit. Further,the rounded edges may also amplify the mixing within the mixing chamber,as described above (as the fluid may be driven against the wall torotate within the chamber, enhancing mixing). In some examples theopenings into the exits from the mixing chambers (e.g., into theconnecting channels) may include a ramp or funnel shape, in whichdiameter of the opening (or the width and depth) may be ramped,funnel-shaped, etc. to provide a more gradual transition between themixing chamber and the channel(s).

Any of the apparatuses described herein may be configured so that themixers are at an angle relative to each other, as described above. Insome examples the angle is approximately 90 degrees (as shown in FIGS.7B-7D), in which the mixing chambers are arranged perpendicular to theconnecting channel. FIGS. 11A-11B illustrate another example of a mixingapparatus in which the angle between the mixing chamber and theconnecting channel is about 135 degrees (see FIG. 11B), when observedfrom the top. Thus in some examples the angle between the mixing chamberand the connecting channel (which may be referred to as a box angle ormixing chamber angle) may be between 90 degrees and 180 degrees, such asabout 100 degrees, about 110 degrees, about 120 degrees, about 130degrees, about 135 degrees, about 140 degrees, about 150 degrees, about160 degrees, etc.). Increasing this angle above 90 degrees may reducedeposition and/or may increase the flow rate (for a lower pressure).Conversely, in some cases it may be preferable to decrease the angle toless than 90 degrees, which may increase mixing efficiency.

As shown in FIG. 11C, there was not a significant change in theZ-Average (e.g., particle size) or PDI between angled and curved (e.g.,135 degrees vs. 90-degree angles). As shown in FIG. 11C, in general, aone-stage mixer (e.g., a mixer having only a single mixing chamber) maysufficiently mix, even with particles. As compared with three-stagedevices that are otherwise similar in dimension, the final particlesizes and PDI values were found to be comparable, or in some instanceseven better, for the one-stage mixer. Thus, the highly compact one-stageapparatus may be used and may result in much less flow restriction.

In some examples, the mixing apparatuses described herein may result insubstantially less deposition over time. For example, apparatuses inwhich the sidewalls and/or bottom and/or top are curved may result inless than 25% deposition per time and/or rate of flow (e.g., less than20%, less than 15%, less than 10%, less than 5%, etc.).

As mentioned, the flow rate may be controlled. The flow rate may alsoimpact the mixing. In general, faster flow rates through theseapparatuses may result in smaller particle sizes, which may reflect theenhanced mixing. This is illustrated in FIG. 13. In FIG. 13, multipleexamples of similar microfluidic mixing apparatuses were examined on thesame microfluidic device substrate (e.g., “chip”), providing parallelrepeats of 1 ml/min (1-4), 2 ml/min (1-4) and 4 ml/min (1-2). Flow ratesmay be tuned to the particle size and/or the dimensions of themicrofluidic device. In FIG. 13, both volume mean (size in nm) and PDIwere reasonably comparable, and showed that as flow rate increased, theparticle sizes decreased.

As discussed above, the ‘step’ or transition from the smaller opening inthe input of the mixing chamber to the mixing chamber and the return tothe small diameter in the output (or connection) channel(s) may enhancethe mixing. However, in some examples, as shown in FIG. 12B, the mixingapparatus may have a same height between the input, output and mixingchamber. FIG. 12A shows another example of a mixing apparatus includingthree mixers connected in series, similar to FIG. 7B. For comparison,FIG. 12B shows an example of an apparatus that does not include the stepfrom a narrower height channel into the deeper box of the mixer. Ingeneral, these mixers may not result in the high level of mixing shownfor other examples, as shown in FIG. 12C. FIG. 12C is a graph showingthe particle size (due to mixing) following multiple runs through amixing apparatus as shown in FIG. 12A (“3 box”) or through a linearmixing channel as shown in FIG. 12B (“3 box planar”), showingsubstantially smaller particle sizes (and therefore more efficientmixing) in the mixing apparatus of FIG. 12A as compared to FIG. 12B.

Optional Examples

Also described herein are additional examples of microfluidicsapparatuses. These apparatuses may include a mixer as described hereinwith one or more additional and optional microfluidic components. Forexample, the outlet channel of a mixer may be in fluid communicationwith one or more of: a pair of final blending chambers, a dialysischamber or an evaporation chamber. A microfluidic path device (e.g.,microfluidic chip) may include a microfluidic dialysis chamber and/ormicrofluidic concentrator. A dialysis chamber and/or concentrator may beextremely compact and efficient and may operate on or within the boundsof a microfluidic apparatus with high efficiency and accuracy. Themixing methods and apparatuses described herein may allow a microfluidicapparatus to also provide, in a single integrated apparatus,purification, dialysis and concentration of one or more therapeuticcomposition (including, but not limited to therapeutic polynucleotides).

For example a microfluidic path device may include: a first plate and asecond plate; a fluid-contacting chamber having a fixed volume formed inthe first plate; a dialysis buffer chamber having a fixed volume formedin the second plate; wherein the fluid-contacting chamber is separatedfrom the dialysis buffer chamber by a dialysis membrane disposed betweenthe first plate and the second plate; and a plurality of pressure portsthrough the first plate; and wherein the fluid-contacting chambercomprises a plurality of channels partitioning the fluid-contactingchamber.

A microfluidic dialysis chambers may have a fluid-contacting chamberformed in the first plate, a dialysis buffer chamber formed in thesecond plate, wherein the fluid-contacting chamber is separated from thedialysis buffer chamber by a dialysis membrane disposed between thefirst plate and the second plate, and a plurality of pressure portsthrough the first plate; and wherein the fluid-contacting chambercomprises a plurality of channels partitioning the fluid-contactingchamber.

Any of these microfluidic dialysis chamber devices may include an inletinto the fluid-contacting chamber and an outlet from thefluid-contacting chamber, wherein the inlet is located on an oppositeside of the length and an opposite side of the width of the fluidcontacting chamber. The inlet may be offset from a side of thefluid-contacting chamber by between about 15% and about 35% of the widthof the fluid-contacting chamber. Any of these dialysis apparatuses mayinclude an elastic membrane sandwiched between the first and secondplates. The periphery of the dialysis membrane may be sealed by anelastic membrane.

For example, a microfluidic path device may include: a first plate and asecond plate; a fluid-contacting chamber having a fixed volume formed inthe first plate; a concentration chamber having a fixed volume formed inthe second plate; wherein the fluid-contacting chamber is separated fromthe concentration chamber by a hydrophobic membrane disposed between thefirst plate and the second plate; and a plurality of pressure portsthrough the first plate; and a plurality of separately-addressablemembrane-driven pumps controlled by the pressure ports and configured todrive fluid through the fluid contacting chamber and dry air through theconcentration chamber.

A microfluidics path device may include: a mixer; a dialysissub-assembly; and a concentrator sub-assembly; wherein the mixerdialysis sub-assembly and concentrator are formed between a first plateand a second plate.

A dialyzer may be formed as part of a microfluidics path device and mayinclude a first chamber separated from a second chamber by a dialysismembrane; the first and/or second chamber may be divided up intochannels. The first channel is configured to pass the fluid to bedialyzed and the second channel is configured to pass a dialyzingsolution. The dialyzing solution may be passed through the secondchannel in a countercurrent direction (e.g., opposite the direction offluid flowing through the first channel.

In some examples the dialyzer is formed between a first plate and secondplate (e.g. a first layer and a second layer) of a microfluidics pathdevice. The first channel may be formed in the first plate and thesecond channel may be formed in the second plate; the dialysis membranemay be sealed between the first and second plates. In some examples anelastic membrane may be sandwiched between the first plate and thesecond plate; the dialysis membrane may be sandwiched between the firstplate and the second plate across an opening in the elastic membrane andmay be sealed (e.g., around its perimeter) by the elastic membrane. Thefirst chamber of the dialyzer may include an inlet on one end and anoutlet on an opposite end of the first chamber. The inlet and outlet maybe offset from the side edges of the first chamber, e.g., at a locationbetween 15-45% of the width of the chamber from the first side edge,where the width is formed between the side edges. Similarly the outletmay be on an opposite side of the chamber (separated by most of thelength of the chamber, and offset from the second side (opposite to thefirst side edge) by an amount that is the same or approximately the sameas the inlet is from the first side edge (e.g., between 15-45% of thewidth of the chamber).

Alternatively, in some examples the elastic membrane is not used to sealthe dialysis membrane. Thus, the dialysis membrane may be held securelyby the engagement of the first plate with the second plate. In someexamples an additional (e.g., third plate) and/or elastic membrane maybe included, e.g., beneath or above the putative first and secondplates.

The first and/or second chambers of the dialyzer may be divided up intoa plurality of channels, as mentioned above. In some examples thechannels may be parallel and may extend in straight lines. In someexamples the channels extend in curved or zig-zag lines. The channelsmay be a uniform cross-sectional diameter, or they may be differentdiameters and/or may have the same cross-sectional diameters.

FIG. 14A shows a perspective view of an example of a dialyzer asdescribed herein. In FIG. 14A, the dialyzer is a sub-region (or dialyzermodule) of a microfluidics device including a first plate 1401, a secondplate 1403 and an elastic membrane 1405 sandwiched between the first andsecond plate. An opening through the elastic membrane (not visible) maybe spanned by a dialysis membrane 1407. The first chamber is separatedfrom the second chamber of the dialyzer by the dialysis membrane 1407,and each chamber shown is divided up into a plurality of parallelchannels extending the length of the first and second chambers.

FIG. 14B is an example of a cross-section through a dialyzer similar tothat shown in FIG. 14A. In FIG. 14B, the dialyzer includes a firstchamber 1411, a second chamber 1413 and a dialysis membrane 1407 betweenthe first and second chambers. An inlet 1422 into the second chamber isalso shown as is an outlet 1423 from the first chamber (the secondchamber outlet and first chamber inlet are not visible in FIG. 14B). Thechannels in each chamber may be formed by the plates from which thechambers are formed. In some examples the channels are on just one side(e.g., the first chamber side); in some examples the channels are onboth sides and may be opposite from each other or may be offset fromeach other.

FIG. 15 is an example of an edge region of a dialyzer such as theexample shown in FIGS. 14A-14B, showing the seal between the upper andlower chambers and the dialysis membrane. In FIG. 15, a first plate 1501includes a first chamber 1511. The first chamber is divided up intoconnected channels. A second plate 1503 is affixed to the bottom of thefirst plate and includes a second chamber 1505 that is also divided intochannels. Channel dividers 1509, 1519 in the first and/or second plateform contact points that crimp a dialysis membrane 1515 therebetween.

At the edge of the dialyzer 1500 an elastic membrane 1521 may besandwiched between the first and second plates. An edge of the elasticmembrane (e.g., a silicone membrane, etc.) may be also secure (e.g.,seal) the dialyzer membrane between the first and second plates, asshown in FIG. 15.

In operation, a dialyzer portion of a microfluidics path device mayinclude an inlet on the sample processing side of the device for driving(by applying pressure) a solution to be dialyzed into the first chamberof the dialyzer. In FIG. 16 the first chamber is shown, divided by aplurality of parallel channels. The inlet 1601 in this example ispositioned in the top, common region of the channel, from which fluid tobe dialyzed may flow towards the outlet 1603. In this example, the inletand outlet are on opposite sides of the width and on opposite sides ofthe length of the chamber. The shading indicate the flow rate (velocity,Z, in cm/s) through the chamber, from the inlet to the outlet. With thisarrangement of inlet and outlet the flow rate is non-uniform, asevidenced by the shading map, showing slower flow through the moreperipheral channel regions.

FIG. 17A shows an example in which the inlet 1701 and outlet 1703 arepositioned slightly inwardly from the long sides of the chamber (e.g.,between 15% and 35% of the width of the chamber, e.g., approximatelyone-quarter of the way into the width) in the common regions at the endsof the chamber, on opposite sides of the width and length. The resultingflow (shown by heat map key FIG. 17B) rates are significantly moreuniform, with slightly faster regions in the channels closest to theinlet and outlet. In the example of FIG. 17A-17C, the maximum flow ratemay be, e.g., about −1.1 cm/sec, while the minimum flow rate may be,e.g., about −0.9 cm/sec. FIG. 17C show the upper common region 1707 thatfeeds into the channels extending the length of the first chamber of thedialyzer; this region may have local regions of higher flow rate 1711,1709. In this example, the pressure between the inlet and outlet maydrop between, e.g., about 14.92 psi (102.87 kPa) and 14.70 psi (101.35kPa), delta of 0.22 psi (1.52 kPa), when the flow is 0.5 ml/min.

In use, the dialyzer may be used to dialyze a solution containing atherapeutic material, e.g., to remove an unwanted material from thesolution. As the solution is flowed through the first chamber, thedialysis solution may be flowed in the same or counter direction as thesecond chamber opposite from the first chamber. The second chamber mayhave essentially the same structure as the first chamber describedabove.

Also described herein are concentrators. A concentrator may have thesame structure as the dialyzer described above, however the membrane maybe a membrane that permits water vapor to pass (allowing evaporationtherethrough) so that air can be flowed across, (hydrophobic membrane)within the second chamber, as fluid is passed through the first chamber,thereby evaporating and concentrating the solution.

In some examples the concentrator is configured to have one or morepathways (channels) through the first, fluid-passing chamber and in somecases, the second chamber through which gas (e.g., air) is passed. FIG.18 illustrates one example of a concentrator apparatus (e.g., aconcentrator sub-assembly for a microfluidics path device). In FIG. 18,the concentrator includes an elongate channel from the inlet 1801 to theoutlet 1803 in the first chamber. A membrane (not shown in FIG. 18) thatallows water vapor to pass extends between the first chamber and asecond chamber. Gas may be passed through the second chamber to removewater and therefore concentrating the solution as it passes through thefirst chamber. The rate of evaporation may be related to the flow ratethrough the concentrator. In FIG. 18, the shading mapping shows thevelocity (cm/s) through the first chamber of the concentrator.

In use, the concentrator may be highly efficient and may concentrate amanufactured dose of therapeutic agent from the microfluidics pathdevice into a concentration range that allows dilution to an injectabledose form (e.g., between 2 mL and 0.1 mL).

The example concentrator shown in FIG. 18 is a 25.4 mm by 25.4 mmsquare. The membrane is a Sterlite PTFE Membrane, 0.22 μm pore size, 37μm thick. In FIG. 18, the input flow rate is approximately 0.5 ml/min.The dialysis membrane transport rate is 0.483 ml/min, and the resultingoutput flow rate is approximately 0.019 ml/min, 1.1 ml/hr. In thisexample, for a velocity between about 4.321 cm/s and 0.160 cm/s, thepressure drop between the inlet and the outlet may be, e.g., 14.96 psi(103.15 kPa) at the inlet and 14.70 psi (101.35 kPa) at the outlet(delta of 1.8 kPa).

As described above, any of the microfluidic path devices describedherein may include one or more dialyzers and/or one or moreconcentrators (dialyzer sub-assembly and/or concentrator sub-assembly).FIG. 19 schematically illustrates a microfluidics path device thatinclude both a series of mixers 1903, e.g., for compounding atherapeutic (e.g., a therapeutic RNA) formed on the microfluidic pathdevice or added to the microfluidic path device, including for adding adelivery vehicle, and a dialyzer 1905 in series between the mixer(s) anda concentrator 1907. A first input 1911, a second input 1913 and a thirdinput 1915 may be inserted as described above in reference to FIG. 4.The final product, following compounding/mixing, dialysis andconcentration, may be output from the concentrator 1931 and may be usedor stored, or further processed. In this fashion the creation ofnanoparticle therapeutics, including dialysis and concentration to afinal injectable form may be done using a single, continuous flowmicrofluidic device with no intermediate storage of materials created inthe formulation process.

FIG. 20 illustrates one example of the relationship between pressure andposition on an exemplary microfluidics path device such as the deviceshown schematically in FIG. 19. In FIG. 20, the input pressures (V1-V4)flow resistances and pressures may be adjusted and/or monitored by thesystem to control the final concentration by regulating theconcentrator.

When a feature or element is herein referred to as being “on” anotherfeature or element, it can be directly on the other feature or elementor intervening features and/or elements may also be present. Incontrast, when a feature or element is referred to as being “directlyon” another feature or element, there are no intervening features orelements present. It will also be understood that, when a feature orelement is referred to as being “connected”, “attached” or “coupled” toanother feature or element, it can be directly connected, attached orcoupled to the other feature or element or intervening features orelements may be present. In contrast, when a feature or element isreferred to as being “directly connected”, “directly attached” or“directly coupled” to another feature or element, there are nointervening features or elements present. Although described or shownwith respect to one example, the features and elements so described orshown can apply to other examples. It will also be appreciated by thoseof skill in the art that references to a structure or feature that isdisposed “adjacent” another feature may have portions that overlap orunderlie the adjacent feature.

Terminology used herein is for the purpose of describing particularexamples only and is not intended to be limiting of the invention. Forexample, as used herein, the singular forms “a”, “an” and “the” areintended to include the plural forms as well, unless the context clearlyindicates otherwise. It will be further understood that the terms“comprises” and/or “comprising,” when used in this specification,specify the presence of stated features, steps, operations, elements,and/or components, but do not preclude the presence or addition of oneor more other features, steps, operations, elements, components, and/orgroups thereof. As used herein, the term “and/or” includes any and allcombinations of one or more of the associated listed items and may beabbreviated as “/”.

Spatially relative terms, such as “under”, “below”, “lower”, “over”,“upper” and the like, may be used herein for ease of description todescribe one element or feature's relationship to another element(s) orfeature(s) as illustrated in the figures. It will be understood that thespatially relative terms are intended to encompass differentorientations of the device in use or operation in addition to theorientation depicted in the figures. For example, if a device in thefigures is inverted, elements described as “under” or “beneath” otherelements or features would then be oriented “over” the other elements orfeatures. Thus, the exemplary term “under” can encompass both anorientation of over and under. The device may be otherwise oriented(rotated 90 degrees or at other orientations) and the spatially relativedescriptors used herein interpreted accordingly. Similarly, the terms“upwardly”, “downwardly”, “vertical”, “horizontal” and the like are usedherein for the purpose of explanation only unless specifically indicatedotherwise.

Although the terms “first” and “second” may be used herein to describevarious features/elements (including steps), these features/elementsshould not be limited by these terms, unless the context indicatesotherwise. These terms may be used to distinguish one feature/elementfrom another feature/element. Thus, a first feature/element discussedbelow could be termed a second feature/element, and similarly, a secondfeature/element discussed below could be termed a first feature/elementwithout departing from the teachings of the present invention.

Throughout this specification and the claims which follow, unless thecontext requires otherwise, the word “comprise”, and examples such as“comprises” and “comprising” means various components can be co jointlyemployed in the methods and articles (e.g., compositions and apparatusesincluding device and methods). For example, the term “comprising” willbe understood to imply the inclusion of any stated elements or steps butnot the exclusion of any other elements or steps.

As used herein in the specification and claims, including as used in theexamples and unless otherwise expressly specified, all numbers may beread as if prefaced by the word “about” or “approximately,” even if theterm does not expressly appear. In all cases, where the phrase “about”or “approximately” is used, the actual value (e.g., amount, distance,etc.) may be used. The phrase “about” or “approximately” may be usedwhen describing magnitude and/or position to indicate that the valueand/or position described is within a reasonable expected range ofvalues and/or positions. For example, a numeric value may have a valuethat is +/−0.1% of the stated value (or range of values), +/−1% of thestated value (or range of values), +/−2% of the stated value (or rangeof values), +/−5% of the stated value (or range of values), +/−10% ofthe stated value (or range of values), etc. Any numerical values givenherein should also be understood to include about or approximately thatvalue, unless the context indicates otherwise. For example, if the value“10” is disclosed, then “about 10” is also disclosed. Any numericalrange recited herein is intended to include all sub-ranges subsumedtherein. It is also understood that when a value is disclosed that “lessthan or equal to” the value, “greater than or equal to the value” andpossible ranges between values are also disclosed, as appropriatelyunderstood by the skilled artisan. For example, if the value “X” isdisclosed the “less than or equal to X” as well as “greater than orequal to X” (e.g., where X is a numerical value) is also disclosed. Itis also understood that the throughout the application, data is providedin a number of different formats, and that this data, representsendpoints and starting points, and ranges for any combination of thedata points. For example, if a particular data point “10” and aparticular data point “15” are disclosed, it is understood that greaterthan, greater than or equal to, less than, less than or equal to, andequal to 10 and 15 are considered disclosed as well as between 10 and15. It is also understood that each unit between two particular unitsare also disclosed. For example, if 10 and 15 are disclosed, then 11,12, 13, and 14 are also disclosed.

Although various illustrative examples are described above, any of anumber of changes may be made to various examples without departing fromthe scope of the invention as described by the claims. For example, theorder in which various described method steps are performed may often bechanged in alternative examples, and in other alternative examples oneor more method steps may be skipped altogether. Optional features ofvarious device and system examples may be included in some examples andnot in others. Therefore, the foregoing description is providedprimarily for exemplary purposes and should not be interpreted to limitthe scope of the invention as it is set forth in the claims.

The examples and illustrations included herein show, by way ofillustration and not of limitation, specific examples in which thesubject matter may be practiced. As mentioned, other examples may beutilized and derived there from, such that structural and logicalsubstitutions and changes may be made without departing from the scopeof this disclosure. Such examples of the inventive subject matter may bereferred to herein individually or collectively by the term “invention”merely for convenience and without intending to voluntarily limit thescope of this application to any single invention or inventive concept,if more than one is, in fact, disclosed. Thus, although specificexamples have been illustrated and described herein, any arrangementcalculated to achieve the same purpose may be substituted for thespecific examples shown. This disclosure is intended to cover any andall adaptations or examples of various examples. Combinations of theabove examples, and other examples not specifically described herein,will be apparent to those of skill in the art upon reviewing the abovedescription.

What is claimed is:
 1. A method of mixing, the method comprising:passing a first fluid and a second fluid through at least one openinginto a mixing chamber within a microfluidic device, so that the firstand second fluids are driven against a wall of the mixing chamber anddriven out of a plane of at least first opening as a mixed fluid, thefirst fluid including one or more therapeutic mRNAs, the second fluidincluding a delivery vehicle for the one or more therapeutic mRNAs; andpassing the mixed fluid out of an outlet opening out of the mixingchamber, wherein the mixing chamber is maintained at a temperature ofbetween 2 and 20 degrees C.
 2. A method of forming a composition, themethod comprising: synthesizing one or more therapeutic mRNAs in amicrofluidic device, wherein the one or more therapeutic mRNAs arewithin a first fluid and a delivery vehicle for the one or moretherapeutic mRNAs is within a second fluid; passing the first fluid andthe second fluid through a first opening into a mixing chamber in themicrofluidic device, so that the first and second fluids are drivenagainst a wall of the mixing chamber and driven out of a plane of thefirst opening to a depth of greater than one times the depth of thefirst opening to form a mixed fluid, wherein the mixing chamber ismaintained at a temperature that is selected to enhance mixing of thetherapeutic mRNA and delivery vehicle; and passing the mixed fluid outof an outlet opening out of the mixing chamber.
 3. The method of claim2, wherein the mixing chamber is maintained at the temperature that isselected to enhance mixing of for the therapeutic mRNA and deliveryvehicle and is between 2 and 20 degrees C.
 4. The method of claim 2,further comprising selecting an enhanced mixing temperature of themixing chamber, wherein selecting the enhanced mixing temperaturecomprises modeling mixing within the mixing chamber in vitro or in vivo.5. The method of claim 2, further comprising selecting an enhancedmixing temperature of the mixing chamber, wherein selecting the enhancedmixing temperature comprises selecting a temperature between about 2 andabout 20 degrees C. based on the delivery vehicle and the one or moretherapeutic mRNAs.
 6. The method of claim 2, wherein the passing thefirst fluid and the second fluid through the first opening into themixing chamber comprises passing the first and second fluids so that thefirst and second fluids are driven against the wall of the mixingchamber and out of a plane transverse to the first opening to the depthof greater than about 2.5 times the depth of the first opening.
 7. Themethod of claim 2, wherein the fluid is driven against the wall of themixing chamber and out of a plane transverse to the first opening to adepth of about 3 or more times the depth of the first opening.
 8. Themethod of claim 2, wherein a top of the first opening is in line with atop of the mixing chamber.
 9. The method of claim 2, wherein the outletopening has a cross-section area that is equal to a cross-sectional areaof the first opening.
 10. The method of claim 2, wherein the mixingchamber is between a first layer and a second layer of the microfluidicdevice.
 11. The method of claim 2, wherein the mixing chamber has alength that is greater than a width, further wherein the length isgreater than 2 times the width of the first opening.
 12. A method offorming a therapeutic composition, the method comprising: passing one ormore therapeutic mRNAs within a first fluid and a delivery vehicle forthe one or more therapeutic mRNAs within a second fluid through a firstopening into a mixing chamber in a microfluidic device, so that thefirst and second fluids are driven against a wall of the mixing chamberand driven out of a plane of the first opening to a depth of greaterthan one times the depth of the first opening to form a mixed fluidcomprising the therapeutic composition; maintaining a temperature of themixing chamber at an enhanced mixing temperature determined to enhancemixing; and passing the mixed fluid out of an outlet opening out of themixing chamber.
 13. The method of claim 12, wherein the enhanced mixingtemperature is between about 2 and about 20 degrees C.
 14. The method ofclaim 12, wherein maintaining comprises determining the enhanced mixingtemperature for the one or more therapeutic mRNAs and/or the deliveryvehicle.
 15. The method of claim 14, further comprising determining theenhanced mixing temperature by modeling mixing in the mixing chamber invitro or in vivo.
 16. The method of claim 14, further comprisingdetermining the enhanced mixing temperature by selecting a temperaturebetween about 2 and about 20 degrees C. having greater mixing ascompared to mixing at other temperatures between about 2 and about 20degrees C.
 17. The method of claim 12, wherein the passing the firstfluid and the second fluid through the first opening into the mixingchamber comprises passing the first and second fluids so that the firstand second fluids are driven against the wall of the mixing chamber andout of a plane transverse to the first opening to the depth of greaterthan about 2.5 times the depth of the first opening.
 18. The method ofclaim 12, wherein the fluid is driven against the wall of the mixingchamber and out of a plane transverse to the first opening to a depth ofabout 3 or more times the depth of the first opening.
 19. The method ofclaim 12, wherein a top of the first opening is in line with a top ofthe mixing chamber.
 20. The method of claim 12, wherein the outletopening has a cross-section area that is equivalent to a cross-sectionalarea of the first opening.
 21. The method of claim 12, wherein themixing chamber is formed between a first layer and a second layer of themicrofluidic device.
 22. The method of claim 12, wherein the mixingchamber has a length that is greater than a width, further wherein thelength is greater than 2 times a width of the first opening.
 23. Amethod of mixing, the method comprising: passing a first fluid and asecond fluid through a first opening into a mixing chamber in amicrofluidic device, so that the first and second fluids are drivenagainst a wall of the mixing chamber and driven out of a plane of thefirst opening to a depth of greater than one times the depth of thefirst opening to form a mixed fluid, the first fluid including one ormore therapeutic mRNAs, the second fluid including a delivery vehiclefor the one or more therapeutic mRNAs; and passing the mixed fluid outof an outlet opening out of the mixing chamber.
 24. The method of claim23, wherein the passing the first fluid and the second fluid through thefirst opening into the mixing chamber comprises passing the first andsecond fluids so that the first and second fluids are driven against thewall of the mixing chamber and out of the plane transverse to the firstopening to the depth of greater than about 2.5 times the depth of thefirst opening.